Devices and systems for ablation therapy

ABSTRACT

Various methods, systems, and devices for treating tissue ablation are disclosed. Some embodiments disclosed herein pertain to methods of treating tumors, systems used for irradiating tissue and tumors with electromagnetic radiation, components and devices of that system, and kits for providing systems used for irradiating tissue and tumors with electromagnetic radiation. In some embodiments, the system provides sub-ablative infrared radiation that is absorbed by nanoparticles. In some embodiments, the nanoparticles absorb the radiation converting it into heat energy. In some embodiments, though the infrared radiation itself may be sub-ablative, the heat energy generated by the nanoparticles is sufficient to cause thermal coagulation, hyperthermia, and/or tissue ablation.

CROSS REFERENCE TO RELATED APPLICATIONS

This patent application is a continuation of U.S. application Ser. No.16/327,292, which is the U.S. National Phase entry of International PCTApplication No. PCT/US2017/066522, filed Dec. 14, 2017, which claims thebenefit of priority to U.S. Provisional Patent Application No.62/435,431, filed Dec. 16, 2016. The forgoing applications are herebyincorporated by reference in their entireties for all purposes.

BACKGROUND Field

Methods, systems, kits, and devices for irradiation of nanoparticles fortherapeutic treatments ablation are disclosed.

Description of the Related Art

Thermal and radiative ablation can be used to burn and/or ablate tissuesfor therapeutic methods. These techniques can be used to ablate cancertissues and tumors.

SUMMARY

Some embodiments disclosed herein pertain to methods, systems, kits, anddevices for therapeutic treatments and/or ablation therapy of tissues.Some embodiments pertain to a laser illuminating system. Any of theembodiments described above, or described elsewhere herein, can includeone or more of the following features.

In some embodiments, the laser illuminating system comprises a laserilluminator assembly. In some embodiments, the laser illuminatorassembly comprises an elongated introducer probe with a domed,transmissive sealed end.

In some embodiments, the laser illuminating system comprises an opticalfiber with a diffuser tip and an optical fiber connector. In someembodiments, the optical fiber connector is configured to engage thelaser illuminator assembly. In some embodiments, when the optical fiberconnector is engaged with the laser illuminator assembly, the diffusertip of the optical fiber is positioned within the laser illuminatorassembly.

In some embodiments, the laser illuminating system comprises a lasersource configured to be in optical communication with the optical fiber.In some embodiments, the laser source is configured to transmitradiation through the optical fiber to the laser illuminator assembly.In some embodiments, when activated, the laser source transmitselectromagnetic radiation through optical fiber and through the sealedend.

In some embodiments, the laser illuminating system comprises a coolantreservoir. In some embodiments, the coolant reservoir is in fluidiccommunication with the laser illuminator assembly. In some embodiments,the laser illuminator assembly comprises a coolant inlet tube configuredto convey coolant from the coolant reservoir to the laser illuminatorassembly.

In some embodiments, the laser illuminating system comprises a pumpconfigured to convey coolant from the coolant reservoir to the laserilluminator assembly via the coolant inlet tube to cool the opticalfiber. In some embodiments, the laser illuminating system comprises acoolant recovery bag in fluidic communication with the laser illuminatorassembly and configured to receive coolant from the laser illuminatorassembly. In some embodiments, the laser illuminator assembly comprisesa coolant outlet tube configured to convey coolant from the laserilluminator assembly to the coolant recovery bag.

In some embodiments, the laser illuminating system comprises an actuatorconfigured to activate and deactivate the laser source. In someembodiments, the actuator is a foot pedal. In some embodiments, theactuator also controls the pump. In some embodiments, the laser and thepump are activated by the actuator substantially simultaneously. In someembodiments, the laser and the pump are deactivated by the actuatorsubstantially simultaneously.

In some embodiments, the coolant inlet tube is tygon material. In someembodiments, the coolant inlet tube is about 4 meters in length. In someembodiments, the coolant inlet tube is configured to allow coolant flowat a low rate. In some embodiments, the coolant inlet tube is configuredto allow coolant flow at a rate of about 8 ml/min.

In some embodiments, the laser source provides a radiation having awavelength that is near infrared wavelength. In some embodiments, thelaser source provides a radiation that has a wavelength ranging fromabout 805 nm to about 810 nm.

In some embodiments, the optical fiber comprises a diffusive portionconfigured to distribute radiation from the optical fiber and out of thelaser illuminator assembly.

In some embodiments, a length of the diffusive portion of the opticalfiber ranges from about 1.0 cm to about 1.8 cm. In some embodiments, thediffusive portion of the optical fiber may be of a length equal to orless than about: 50 mm, 30 mm, 18 mm, 10 mm, values between theaforementioned values, or ranges including and/or spanning those values.

Some embodiments disclosed herein pertain to a method of treating aprostate tumor. Any of the embodiments described above, or describedelsewhere herein, can include one or more of the following features.

In some embodiments, the method comprises injecting and/or infusingnanoparticles into a patient systemically. In some embodiments, thenanoparticles are adapted to transduce infrared light into heat energy.In some embodiments, the method comprises allowing the nanoparticles topreferentially accumulate in the prostate tumor. In some embodiments,the method comprises inserting a trocar assembly comprising a trocar anda catheter sheathed around the trocar into the patient at a firstinsertion point. In some embodiments, the method comprises positioningthe trocar assembly in the patient by passing the trocar assemblythrough the prostate tumor such that the trocar assembly passes througha proximal face of the tumor and terminates at a distal side of thetumor creating a first path within the tumor. In some embodiments, themethod comprises removing the trocar from the patient and leaving thecatheter in the patient within the first path. In some embodiments, themethod comprises inserting an introducer probe of a laser illuminatorassembly into the catheter. In some embodiments, the laser illuminatorassembly comprises an introducer probe, the introducer probe beingelongate and comprising a first lumen and terminating in a sealed domedend configured to allow laser light transmission. In some embodiments,the laser illuminator assembly comprises an internal tube located withinthe first lumen of the introducer probe, the internal tube comprising asecond lumen. In some embodiments, the laser illuminator assemblycomprises an optical fiber configured to receive photons from a lasersource, wherein the optical fiber is positioned within the second lumenof the introducer probe and is configured to transmit laser radiationthrough the domed end of the introducer probe. In some embodiments, thefirst lumen is in fluidic communication with the second lumen.

In some embodiments, the method comprises guiding the introducer probeto a first position within the first path in the tumor, wherein thefirst position is located at or near the distal side of the tumor. Insome embodiments, the method comprises activating the laser source whenthe introducer probe is at the first position within the first path togenerate non-ablative infrared radiation at the first position for afirst period of time wherein the infrared radiation causes heating ofthe nanoparticles to an ablative temperature. In some embodiments, themethod comprises withdrawing the catheter and the introducer probe to asecond position within the first path in the tumor, the second positionbeing proximally located relative to the first position. In someembodiments, the method comprises activating the laser source when theintroducer probe is at the second position to generate non-ablativeinfrared radiation for a second period of time wherein the infraredradiation causes heating of the nanoparticles to an ablativetemperature.

In some embodiments, the method comprises removing the catheter and thelaser illuminator from the first path. In some embodiments, the methodcomprises inserting the trocar assembly into the patient at a secondinsertion point that is laterally disposed on the proximal side of thetumor from the first insertion point. In some embodiments, the methodcomprises positioning the trocar assembly in the patient by passing thetrocar assembly through the prostate tumor such that the trocar assemblypasses through the proximal face of the tumor and terminates at thedistal side of the tumor and creates a second path through the tumor. Insome embodiments, the method comprises inserting the introducer probeinto the catheter. In some embodiments, the method comprises guiding theintroducer probe to a first position within the second path in thetumor, wherein the first position is located near the distal side of thetumor. In some embodiments, the method comprises activating the lasersource when the introducer probe is at the first position within thesecond path to generate non-ablative infrared radiation at the firstposition of the second path for a third period of time wherein theinfrared radiation causes heating of the nanoparticles to an ablativetemperature. In some embodiments, the method comprises withdrawing thecatheter and the introducer probe to a second position within the secondpath in the tumor, the second position being proximally located relativeto the first position in the second path. In some embodiments, themethod comprises activating the laser source when the introducer probeis at the second position of the second path to generate non-ablativeinfrared radiation for a fourth period of time wherein the infraredradiation causes heating of the nanoparticles to an ablativetemperature.

In some embodiments, the first position and the second position of thefirst path are about 8 mm apart. In some embodiments, the first positionand the second position of the second path are about 8 mm apart. In someembodiments, a template grid is used to position the trocar assembly atthe first insertion point and at the second insertion point.

In some embodiments, the method comprises inserting the trocar assemblyinto the patient at additional insertion points that are laterallydisposed on the proximal side of the tumor from the first insertionpoint and second insertion points.

In some embodiments, the template grid is used to position the trocarassembly at the additional insertion points.

In some embodiments, the laser illuminator assembly comprises a coolantoutlet in fluidic communication the first lumen and a coolant inlet influidic communication with the second lumen wherein the laserilluminator assembly is configured to allow the passage of a coolantfrom the coolant inlet through the second lumen into the first lumen andout of the coolant outlet.

In some embodiments, the laser illuminator is activated by an actuatorthat is controlled by a user. In some embodiments, the user activatesthe laser illuminator using the actuator, coolant flows into the firstinlet of the laser illuminator assembly and wherein when the laserilluminator is not active, coolant does not flow laser illuminatorassembly. In some embodiments, the actuator is a foot pedal.

In some embodiments, the laser illuminator emits radiation having a nearinfrared wavelength. In some embodiments, the laser illuminator emitsradiation having a near infrared wavelength ranging from about 805 nm toabout 810 nm. In some embodiments, the laser illuminator emits radiationthat is of insufficient power and/or intensity to induce photothermalcoagulation of tissue. In some embodiments, the optical fiber comprisesa diffuser tip that distributes the non-ablative infrared radiationwithin the tumor. In some embodiments radiation is distributed laterallyor sideways from the diffuser tip. In some embodiments, radiation is nottransmitted through the tip and/or terminus of the optical fiber and/ordiffuser tip. In some embodiments, radiation is transmitted through thetip and/or terminus of the optical fiber and/or diffuser tip and throughthe sealed domed end. In some embodiments, the laser illuminator emitsradiation between about 3.5 W/cm and about 4.5 W/cm of the diffuser tip.

Some embodiments pertain to a laser illuminator device comprising anintroducer probe. Any of the embodiments described above, or describedelsewhere herein, can include one or more of the following features.

In some embodiments, the introducer probe comprises a first lumenterminating in a sealed domed end configured to allow laser lighttransmission. In some embodiments, the introducer probe comprises aninternal tube located within the first lumen of the introducer probe,the internal tube comprising a second lumen In some embodiments, theintroducer probe comprises an optical fiber. In some embodiments, theoptical fiber is positioned within the second lumen. In someembodiments, the optical fiber can transmit laser radiation through thedomed end of the introducer probe. In some embodiments, the first lumenis in fluidic communication with the second lumen.

In some embodiments, the device comprises a coolant outlet in fluidiccommunication the first lumen and a coolant inlet in fluidiccommunication with the second lumen. In some embodiments, the devicecomprises the laser illuminator assembly is configured to allow thepassage of a coolant from the coolant inlet through the second lumeninto the first lumen and out of the coolant outlet. In some embodiments,the fluid inlet and the fluid outlet are configured to interact withdifferent connectors to prevent improper routing of coolant through thelaser illuminator device. In some embodiments, the fluid inlet and thefluid outlet are of different sexes. In some embodiments, the fluidinlet comprises a male connector and the fluid outlet comprises a femaleconnector.

In some embodiments, the optical fiber comprises a diffusive portionconfigured to distribute radiation from the optical fiber and out of thelaser illuminator assembly. In some embodiments, the length of thediffusive portion of the optical fiber ranges from about 1.0 cm to about1.8 cm. In some embodiments, the diffusive portion of the optical fibermay be of a length equal to or less than about: 50 mm, 30 mm, 18 mm, 10mm, values between the aforementioned values, or ranges including and/orspanning those values.

In some embodiments, the outside of the probe is graduated. In someembodiments, the graduations are about 4 mm apart.

Some embodiments pertain to a method of treating a tumor. Any of theembodiments described above, or described elsewhere herein, can includeone or more of the following features.

In some embodiments, the method comprises injecting nanoparticles into apatient systemically wherein the nanoparticles are adapted to transduceinfrared light into heat energy.

In some embodiments, the method comprises allowing the nanoparticles topreferentially accumulate in the tumor.

In some embodiments, the method comprises inserting a trocar assemblycomprising a trocar and a catheter sheathed around the trocar into thepatient at a first insertion point.

In some embodiments, the method comprises positioning the trocarassembly in the patient by passing the trocar assembly through the tumorsuch that the trocar assembly passes through a proximal face of thetumor and terminates at a distal side of the tumor and creates a firstpath within the tumor.

In some embodiments, the method comprises removing the trocar from thepatient and leaving the catheter in the patient within the first path.

In some embodiments, the method comprises inserting an introducer probeof a laser illuminator assembly into the catheter wherein the laserilluminator assembly comprises an introducer probe. In some embodiments,the introducer probe comprises a first lumen and terminating in a sealeddomed end configured to allow laser light transmission. In someembodiments, the the introducer probe comprises an internal tube locatedwithin the first lumen of the introducer probe, the internal tubecomprising a second lumen. In some embodiments, the method comprises theintroducer probe comprises an optical fiber configured to receivephotons from a laser source. In some embodiments, the optical fiber ispositioned within the second lumen and configured to transmit laserradiation through the domed end of the introducer probe. In someembodiments, the first lumen is in fluidic communication with the secondlumen.

In some embodiments, the method comprises guiding the introducer probeto a first position within the first path in the tumor, wherein thefirst position is located near the distal side of the tumor.

In some embodiments, the method comprises activating the laser sourcewhen the introducer probe is at the first position within the first pathto generate subablative infrared radiation at the first position for afirst period of time thereby heating the nanoparticles to an ablativetemperature.

In some embodiments, the method comprises withdrawing the catheter andthe introducer probe to a second position within the first path in thetumor, the second position being proximally located relative to thefirst position

In some embodiments, the method comprises activating the laser sourcewhen the introducer probe is at the second position to generatesubablative infrared radiation for a second period of time therebyheating the nanoparticles to an ablative temperature.

Some embodiments pertain to a method of treating a tumor. Any of theembodiments described above, or described elsewhere herein, can includeone or more of the following features. In some embodiments, the methodcomprises obtaining a laser illuminator comprising an introducer probe.In some embodiments, the introducer probe comprises a domed-end and anoptical fiber, the optical fiber being in optical communication with alaser source. In some embodiments, the method comprises positioning theintroducer probe in a tissue comprising the tumor by passing theintroducer probe through a proximal face of the tissue to a distal sideof the tissue to a first position. In some embodiments, the methodcomprises activating the laser source while the introducer probe is atthe first position to transmit sub-ablative infrared radiation to thetissue for a first period of time. In some embodiments, the methodcomprises withdrawing the introducer probe to a second position in thetissue, the second position being proximally located relative to thefirst position. In some embodiments, the method comprises activating thelaser source when the introducer probe is at the second position totransmit sub-ablative infrared radiation to the tissue for a secondperiod of time.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 illustrates an embodiment of a laser illuminating system.

FIG. 2A illustrates an embodiment of a laser catheter assembly.

FIGS. 2A1 and 2A2 illustrate expanded views of the laser catheterassembly shown in FIG. 2A.

FIG. 2B is a view of a laser catheter assembly as shown in FIG. 2A.

FIG. 3A illustrates an embodiment of an optical fiber that can beinserted into the laser catheter assembly of FIG. 2A.

FIG. 3B is a view of an optical fiber as shown in FIG. 3A.

FIG. 4 is a view of an embodiment of a coolant inlet conduit.

FIG. 5A illustrates an embodiment of a coolant recovery bag.

FIG. 5B is a view of a coolant recovery bag as shown in FIG. 5A.

FIGS. 6A-6B4 illustrate views of a trocar sleeve assembly.

FIG. 7A-7J illustrate the insertion and illumination of a test tissueusing an embodiment of a laser catheter assembly described herein.

FIG. 8A depicts an embodiment of a hexagonal grid template for laserprobe placement.

FIG. 8B depicts an embodiment of a square grid template.

FIG. 8C depicts an embodiment of laser exposure regions using ahexagonal grid template with 7 mm spacings between grid apertures.

FIG. 8D depicts an embodiment of laser exposure regions using a squaregrid template with 3 mm spacings between grid apertures.

FIG. 8E shows a view of a disassembled three-part square grid.

FIG. 8F is a view of an embodiment of a monolithic hexagonal grid.

FIG. 8G is a view of an embodiment of a three-part square grid.

FIGS. 9A-9G illustrate components of an embodiment of a laserilluminating system kit.

FIGS. 10A-10B are photographs of an experimental set-up for the testingof a laser catheter having a conical tip and a laser catheter assemblyhaving a transmissive tip.

FIGS. 11A-11B are graphs showing the heating of a laser catheter havinga conical tip (11A) and of a laser catheter assembly having a roundedtransmissive tip (11B).

FIGS. 12A-12B depict thermal images of the distal end of a lasercatheter having a conical tip after 6.0 W irradiation.

FIGS. 12C-12D depict thermal images of the distal end of a lasercatheter having a domed tip after 6.0 W irradiation.

FIG. 13 depicts the heating of a conical tip laser catheter when anoptical fiber having an 18 mm diffuser is used.

FIGS. 14A-14I are photographs of 9 whole-mount sections of patients'prostates (scale bars=1 cm).

FIG. 15 is a graph showing the relative accumulation of nanoparticles insamples tumor tissue versus healthy tissue from two patients.

DETAILED DESCRIPTION

Various methods, systems, and devices for treating tumors are disclosed.Some embodiments disclosed herein pertain to methods of treating tumors,systems used for irradiating tissue and tumors with electromagneticradiation, components and devices of that system, and kits for providingsystems used for irradiating tissue and tumors with electromagneticradiation. In some embodiments, the system provides non-ablativeinfrared radiation (e.g., radiation that is of insufficient intensity toablate tissue by itself and/or sub-ablative radiation) that is absorbedby nanoparticles. In some embodiments, the nanoparticles absorb theradiation converting it into heat energy. In some embodiments, thoughthe infrared radiation itself may be sub-ablative, the heat energygenerated by the nanoparticles is sufficient to cause thermalcoagulation, hyperthermia, and/or tissue ablation. A variety of methods,devices, systems, and kits for treating tumors and ablating tissue aredescribed below to illustrate various examples that may be employed toachieve one or more desired improvements. These examples are onlyillustrative and are not intended in any way to restrict the generalinventions presented and the various aspects and features of theseinventions. Furthermore, the phraseology and terminology used herein isfor the purpose of description and should not be regarded as limiting.No features, structure, or step disclosed herein is essential orindispensable. Any of the systems or methods disclosed herein canexclude one or more steps or features described herein.

Optical properties govern how optical wavelength photons interact withbiological tissue. These are optical scatter and optical absorption.Scatter results when a photon encounters a change in index ofrefraction, such as at the membrane of a cell. A scattered photon willcontinue to travel through the tissue, but in an altered direction.Absorption results in the deposition of the photon's energy intowhatever absorbed it, such as a hemoglobin molecule or cell organelle.The energy of the absorbed photon is generally converted into heat,which radiates away from the absorption site.

Absorption of photon energy can cause photocoagulation, which results inthe unraveling of proteins, leading to a dramatic increase in opticalscatter and reduction in the ability of light to penetrate into tissue.The change of egg white from clear to opaque when heated in a frying panis a well-known example of this phenomenon. Photothermal coagulation asa therapeutic method can make use of the ability of laser energy to betransmitted through optical fiber in order to deliver particular amountsof energy interstitially into tissue. Laser Interstitial Thermal Therapy(LITT) is the technique of delivering sufficient optical power todirectly generate thermal coagulation in tissue. Essentially, opticalenergy is delivered into tissue at a rate greater than the body'sability to remove the resulting heat. This heat can result inhyperthermia and tissue ablation.

However, the effective treatment depth of LITT and other photon-basedtherapies can be hindered by light scatter and absorption in tissues(including that caused by thermal coagulation). This scatter andabsorption can result in light intensity that diminishes exponentiallywith increased distance from the light source into tissue. A furtherconstraint is that light intensity, or irradiance (measured in W/cm²),also declines and/or decreases in the radial direction when delivered bya one-dimensional source (e.g., optical fiber diffusers used to deliverlaser light interstitially into tissue). The net result is that opticalirradiance is higher immediately adjacent to the optical sourcedelivering it and much lower in areas just outside the immediatevicinity of the optical source (e.g., a diffuser). Photon-basedprocesses of phototherapy are also non-specific; the shape of the regionof coagulation is a function of the shape of the energy source, and thevolume of the region of coagulation is dependent upon the total energydeposited. For example, current laser catheters used for photon-basedprocesses use optical fiber diffusers and 12-15 W of power to generateellipsoidal coagulation zones around the diffuser. Thus, selectivity totreat target tissue is low.

Further, because current systems require high power irradiance, highlaser temperatures occur that can destroy and/or deform laser deliverycatheters. Active cooling is used to prevent carbonization of the tissueimmediately around the laser delivery catheter and/or to preventinstrument damage. However, these systems do not actively regulatecoolant used to cool these laser catheters and typically allow a flow of˜15-20 mL/min of room temperature saline in a thin jacket surroundingthe optical fiber diffuser to prevent tissue carbonization on the lasercatheter. An uncontrolled coolant flow can lead to cooling of tissuesexposed to the cooling source between laser applications.

Some embodiments disclosed herein pertain to methods, devices, systems,and kits for using non-ablative radiation to generate particle-directedphotothermal coagulation (e.g., using nanoparticles or other agents). Insome embodiments, the disclosed techniques and devices allow improvedselectivity in targeting of tissues and in effectively treating tissues.Some embodiments disclosed herein pertain to systems and devices used togenerate radiation at a site where photothermal coagulation,hyperthermia, and/or tissue ablation is desired.

In some embodiments, the methods and devices pertain toparticle-directed (e.g., with nanoparticles) photothermal coagulationused for treating tumors. In some embodiments, the methods involveinjecting nanoparticles into a patient with a tumor (or another tissuethat is to be targeted). In some embodiments, the nanoparticles areallowed to accumulate in the tumor over a defined period of time. Insome embodiments, once the nanoparticles have accumulated in a site ofinterest, the laser probe of a laser catheter assembly is positioned(e.g., inserted, placed, etc.) into or near the site of interest (e.g.,in or near a tumor). In some embodiments, the laser catheter assembly isactivated to deliver electromagnetic radiation (e.g., ultraviolet light,visible light, near-infrared light, far-infrared light, microwave, etc.)to the nanoparticles. In some embodiments, the radiation is infraredradiation. In some embodiments, the laser catheter assembly deliversradiation that is of insufficient intensity to cause photothermalcoagulation (e.g., radiation that is non-ablative radiation and/orsub-ablative), hyperthermia, and/or tissue ablation by itself (e.g., inthe absence of the nanoparticles). In some embodiments, the radiationintensity is transduced into heat energy by the nanoparticles. In someembodiments, the heat transduced by the nanoparticles is sufficient tocause ablative hyperthermia, tissue coagulation, and/or tissue ablation.

In some embodiments, the nanoparticles used in the disclosed methods aredesigned to absorb infrared radiation and convert it to heat energy. Insome embodiments, gold nanoshells (e.g., AuroShells, etc.) are used asnanoparticles that transduce the sub-ablative infrared radiation toablative temperatures. While, gold nanoshells (e.g., AuroShells, etc.)are used as a representative nanoparticle for illustration, it should benoted that any nanoparticle (or microparticle) that absorbs infraredphotons and transduces those photons to heat energy is envisioned.Without being bound to any particular theory, it is believed thatabsorption of a photon by a nanoshell effectively annihilates the photonand results in the transduction of its energy into heat, which isemitted into the surrounding tissue. When a photon is scattered by aparticle (e.g., not absorbed), the scattered photon is available forabsorption elsewhere (e.g., by tissue, another nanoshell, etc.).Transducing nanoparticles include, among others: nanoshells (includinggold-shell silica core nanoshells such as Auroshells, gold-gold sulfidenanoshells and other variants), solid nanospheres (gold, silver, etc.),metal nanorods (gold, silver, etc.), nanostars, hollow nanoparticles,nanocages, elliptical “nanorice,” carbon particles, fullerenes, carbonfullerenes, metallic nanoparticles, metal colloids, carbon particles,carbon nanotubes, buckyballs, and any combination thereof.

In some embodiments, the methods disclosed herein are used to targettissues for treatment. In some embodiments, the target tissue is tumortissue. In some embodiments, the tumor targets include tumors caused bycancer. In some embodiments, the tumors are those caused by colorectalcancer, brain cancer, lung cancer, breast cancer, head and neck cancer,pancreatic cancer, ovarian cancer, melanoma cancer, prostate cancer, andother forms of cancer. In some embodiments, the techniques disclosedherein are suitable for treating tumors in a tissue and/or forpreserving the function of healthy tissue while destroying theunderlying tumor tissue. For example, in some embodiments, thetechniques and devices disclosed herein can be used to specificallytarget tumor tissues or dysfunctional tissues. The loss of function of aparticular healthy tissue can have devastating effects for a patient'squality of life. For example, surgical manipulation to remove cancertumor tissue from the throat can cause loss of speech. Surgicalmanipulation to remove cancer tumor tissue from the prostate can causeloss of sexual function. In current methods of ablation, tissues areheated based on the placement of a heating instrument in a tumor. Theheating element is activated, thereby killing tissue surrounding it,including healthy tissue. In some embodiments, the treatments disclosedherein can partially, substantially, and/or fully preserve the structureand/or function of the non-diseased underlying healthy tissue to promoteor substantially preserve normal function of those underlying tissues.

In some embodiments, the methods involve injecting (e.g., infusing)nanoparticles into the patient systemically. Systemic introduction caninvolve the introduction of nanoparticles into the circulatory systemand/or at a site within the body but away from or remote from the targetsite. In some embodiments, the nanoparticles can be introduced to apatient via parenteral administration routes (e.g., injection via theintravenous, intramuscular, sub-cutaneous, intralesional,intraperitoneal, etc.). These sites can be located in areas of thepatient's body that are not proximally located to the site of treatment(e.g., at sites in the body other than the tumor site). For instance,nanoparticles accumulate preferentially within tumors largely as aresult of their size and passive extravasation from the leaky, chaoticand immature vasculature of tumors; a phenomenon referred to as the“enhanced permeability and retention” (EPR) effect. In some embodiments,this passive accumulation allows targeted deposition of the radiationtransducers and affords photothermal coagulation therapy that istumor-specific.

In some embodiments, after being introduced to the body, thenanoparticles are allowed to passively accumulate at a tumor. In someembodiments, this passive accumulation is achieved by the passage of adefined period of time. In some embodiments, the nanoparticles areallowed to accumulate in the tumor for a period of time ranging frombetween equal to or at least about 12 hours and/or less than or equal toabout 36 hours after infusion and/or injection. In some embodiments, thenanoparticles are allowed to accumulate in the tumor site for a periodof at least: about 12 hours, 24 hours, about 36, or ranges includingand/or spanning the aforementioned values.

In some embodiments, the nanoparticles accumulate in the perivascularspace of tumor neovasculature and serve as foci for laser energy. Insome embodiments, after accumulation at a site of interest, laser and/orelectromagnetic energy is used to heat the nanoparticles. In someembodiments, this laser energy (e.g., electromagnetic energy) heats thenanoparticles to a sufficient temperature to cause thermal coagulation,hyperthermia, and/or ablation of target tissue.

In some embodiments, laser energy is generated at a target site fortreatment using a laser illuminating system 100 as shown in FIG. 1. Insome embodiments, as shown in FIG. 1, the laser illuminating system 100comprises a laser catheter assembly 101 (e.g., a laser illuminator). Insome embodiments, the laser illuminating system further comprises one ormore of an illuminating system 200 and a cooling system 300. In someembodiments, the illuminating system 200 comprises an optical fiber 202and a laser source 203. In some embodiments, the optical fiber 202 isconfigured to connect to, to be in optical communication with, and/or toreceive laser energy from the laser source 203. In some embodiments, asdisclosed elsewhere herein, the laser source, the optical fiber, and/orthe laser catheter are in optical communication. In some embodiments,the cooling system comprises one or more of a coolant reservoir 305, acoolant pump 307, and/or a coolant recovery bag 309. In someembodiments, as disclosed elsewhere herein, the coolant reservoir, thelaser catheter assembly, and/or the coolant recovery bag are configuredto be in fluidic communication with each other. In some embodiments, thelaser illuminating system includes the laser catheter assembly but lacksone or more of the other features, such as the illuminating systemand/or the coolant delivery system and components thereof.

In some embodiments, as shown in FIG. 1, the laser catheter assembly 101is configured to receive coolant via a coolant inlet connector 104. Insome embodiments, the laser illuminating system 100 comprises a coolantreservoir 305 (e.g., a bag, bottle, etc.). In some embodiments, thecoolant reservoir 305 is in fluidic communication with the coolant inletconnector 104 via a coolant inlet conduit 306. In some embodiments,coolant from the coolant reservoir 305 is transferred into the lasercatheter assembly 101 via the coolant inlet connector 104 using acoolant pump 307. In some embodiments, the coolant inlet conduit 306 hasan inlet conduit connector 310 that is configured to interact with thecoolant inlet connector 104.

In some embodiments, the laser catheter assembly 101 is configured toexpel coolant via a coolant outlet connector 108. In some embodiments,the laser illuminating system 100 comprises a coolant recovery bag 309(e.g., a bag, bottle, etc.). In some embodiments, the coolant recoverybag 309 is in fluidic communication with the coolant outlet connector108 via a coolant outlet conduit 311. In some embodiments, coolant fromthe laser catheter assembly 101 is transferred into the coolant recoverybag 309 via the coolant outlet connector 108. In some embodiments, thecoolant outlet conduit 311 has an outlet conduit connector 312 that isconfigured to interact with the coolant outlet connector 108.

In some embodiments, as shown in FIG. 2A, the inlet and outletconnectors of the laser catheter assembly 101 are of different sex. Insome embodiments, this configuration can prevent incorrect connectionand/or mismatching of the inlet and outlet connectors of the lasercatheter assembly 101 to the coolant supply and recovery attachments(e.g., preventing backward connection). For example, as shown in FIG. 1,the coolant inlet connector 104 can be a female connector with a femalereceiving portion 104′ and the coolant supply inlet 310 can have a maleconnection with a male protrusion 315 and optionally a shroud 316 (e.g.,a hood, a threaded shroud, etc.) while the coolant outlet connector 108can be a male connector with a male protrusion 108′ and optionally ashroud 108″ (e.g., a hood, a threaded shroud, etc.) and the coolantoutlet conduit connector 324 can have a female connection with a femalereceiving portion 325. In some embodiments, the coolant inlet connector104 can be a male connector while the coolant outlet connector 108 canbe a female connector (not shown). In some embodiments, instead of or inaddition to having different sexes, the inlet connector 104 and outletconnector 108 can be color-coded to match a color on the inlet conduitconnector 310 and the outlet conduit connector 324 (not shown). Forexample, in some embodiments, the inlet connector 104 and the inletconduit connector 310 could be one color (e.g., red, orange, yellow,green, cyan, blue, indigo, violet, purple, magenta, pink, brown, white,gray, black), and the outlet connector 108 and the outlet conduitconnector 324 could be of another different color (e.g., red, orange,yellow, green, cyan, blue, indigo, violet, purple, magenta, pink, brown,white, gray, black). In some embodiments, the male and female connectorscan be luer connectors (which in some embodiments can include an ISO594-compliant luer taper). In some embodiments, the inlet and outletconnectors are not of a different sex.

As shown in FIGS. 2A and 2B, in some embodiments, the laser catheterassembly 101 comprises an introducer probe 113. In some embodiments, asshown in FIG. 2A, the laser catheter assembly 101 comprises one or moreof an outlet arm unit 125, an outlet arm 126, and inlet arm unit 130,and an inlet arm 131. In some embodiments, the introducer probe 113 isan elongated tube that extends from a proximal introducer probeconnector seal 135 (e.g., a seal, sleeve, etc.) to a sealed end 115 ofthe introducer probe 113.

In some embodiments, the introducer probe 113 comprises an outer tubularsection 114. In some embodiments, as shown in FIGS. 2A and 2B, the outertubular section 114 is a continuous material (e.g., a single piecemolded out of a single material, a unitary structure, etc.). In someembodiments, the outer tubular section 114 is transparent orsubstantially transparent to certain wavelengths of electromagneticradiation, for example, one or more of ultraviolet light, visible light,near-infrared light, far-infrared light, and/or microwave radiation.

In some embodiments, the outer tubular section 114 comprises a sealedend 115. In some embodiments, the sealed end 115 is clear, opticallyand/or infrared transparent, and/or substantially optically and/orinfrared transparent. In some embodiments, the sealed end 115 istransparent or substantially transparent to certain wavelengths ofelectromagnetic radiation, for example, one or more of ultravioletlight, visible light, near-infrared ight, far-infrared light, and/ormicrowave radiation. In some embodiments, the sealed end 115 istransmissive. In some embodiments, the sealed end 115 allowselectromagnetic radiation from the laser source 203 to be transmittedthrough it (e.g., via a diffuser tip 204 as disclosed elsewhere herein).In some embodiments, as shown in FIG. 2A2, the sealed end 115 is shapedto distribute light from the optical fiber 202 in line with theintroducer probe 113, in a conical distribution 140 expanding outwardlyand distally from the sealed end 115, or in a semi-sphericaldistribution 141 expanding outwardly and distally from the sealed end115. In some embodiments, the distribution of light (conically orsemi-spherically) is diffused such that, within the distribution, theamount of radiation at a given distance is substantially orapproximately of the same intensity (e.g., at points 140A and 140Band/or at points 141C and 141D. In some embodiments, the end 115 isconfigured to allow radiation and/or light to pass through it withoutsubstantially absorbing it.

In some embodiments, the optical fiber tip 204 is configured to inhibitthe passage of radiation through the tip and/or the optical fiber tip204 substantially blocks radiation. In some embodiments, the diffusertip 223 is configured to emit a majority and/or substantially all and/orall of the radiation received via the radiation source laterally (e.g.,sideways from the diffuser tip) and not along the path of the opticalfiber 202 (e.g., through the optical fiber tip 204). In someembodiments, a diffusive tip that emits radiation laterally (e.g., tothe sides) advantageously allows the treatment of tissues adjacent tothe diffuser tip 223. In some embodiments, this configuration preventsand/or lowers the amount of heating and/or of irradiation of tissuedirectly in front of the fiber tip 204.

In some embodiments, as noted elsewhere herein, the diffuser tip 223 isconfigured to distribute electromagnetic radiation laterally from theintroducer probe. In some embodiments, the intensity of electromagneticradiation from the diffuser is approximately or substantially equal atequal distances from the diffuser tip 223. In some embodiments, lightemitted from the introducer probe 113 is distributed and/or not focused.In some embodiments, light emitted from the introducer probe 113 isdistributed substantially evenly. In some embodiments, because light isdistributed from the diffuser along the surface of the diffuser, theradiation emitted does not cause shadows (e.g., places where theradiation is blocked by a component of the laser catheter, etc.). Insome embodiments, the laser catheter assembly and/or the diffuser tiplacks a focusing lens and does not comprise a mirror.

In some embodiments, the sealed end is domed (e.g., hemispherical,having the shape of a hemisphere, semi-spherical, dome-shaped, etc.). Insome embodiments, as described elsewhere herein, the sealed-end istransmissive. In some embodiments, transmissive means allowing all,substantially all, or part of the electromagnetic radiation from thediffuser tip 223 to pass. In some embodiments, the outer tubular section114 is continuous with the sealed end 115 (e.g., the sealed end and theouter tubular section are a single piece molded out of a singlematerial, a unitary structure, etc.). In some embodiments, thetransmissive sealed end 115 has the benefit of reducing the build-up ofheat in the tip of the probe. This feature helps avoid melting of theprobe and also allows the laser to be distributed into tissue along thedirection of the probe. In some embodiments, the sealed end is notcone-shaped and/or not a ground material (e.g., a scattering material,an opaque or substantially opaque material, etc.). In some embodiments,it has been found that round and/or cone configurations do not allowradiation to pass through the introducer probe. In some embodiments, ithas been found ground and/or conical configurations can concentrateradiation causing hot spots and heating that can lead to warping and/orcharring of a probe and/or burning of tissue around the probe.

In some embodiments, the domed tip is prepared using radio frequency. Insome embodiments, the domed tip is formed from a nylon extrusion, whichis placed over a mandrel, and then inserted into a stainless steel die.In some embodiments, the die is heated with RF energy, while theextrusion is simultaneously pushed into the cavity usingpneumatically-actuated grippers, which causes the tip of the extrusionto be reflowed/reshaped over the end of the mandrel.” In someembodiments, the RF machine is set with temperature, pressure, and timesettings that are specific to extrusion so it can produce veryrepeatable tips. In some embodiments, the tip is not hemisphericallyshaped, but is another shape that allows the passage of radiationwithout substantial build-up of heat or concentration of radiation(e.g., a rounded cubical end shape, a cubical end shape, a roundedcylinder end shape, a cylinder end shape, etc.).

In some embodiments, as shown in FIG. 2A1, the outer tubular section 114comprises a lumen 116 (e.g., a first lumen). In some embodiments, aninternal tube 117 resides within the first lumen 116. In someembodiments, the internal tube 117 comprises a second lumen 118.

In some embodiments, as shown in FIG. 2A and FIG. 2B, the laser catheterassembly 101 is configured to receive coolant via the coolant inletconnector 104, though a catheter inlet conduit 132, through the inletarm unit 131, and into a body of the inlet arm unit 130. The coolantthen travels via the internal tube 117, to the open pool 119, throughthe first lumen 116, through the outlet arm unit 125, through the outletarm, into the catheter outlet conduit, and out via the coolant outletconnector 108. In other words, in some embodiments, one or more of thecoolant inlet connector 104, the catheter inlet conduit 132, the inletarm unit 131, the inlet arm unit 130, the internal tube 117, the openpool 119, the first lumen 116, the outlet arm unit 125, the outlet arm,the catheter outlet conduit, and/or the coolant outlet connector 108 arein fluidic communication.

In some embodiments, the introducer probe 113 extends from a proximalend to a distal end, the sealed domed end 115 of the outer tubularsection 114 being located at the distal end. In some embodiments, theinternal tube 117 terminates a distance away from the sealed domed end115 leaving an open pool 119 at the distal end of the introducer probe113. In some embodiments, when the optical fiber is positioned in theintroducer probe 113, the terminal end of the diffuser tip 223terminates at or approximately at the distal end of the internal tube117. In some embodiments, a portion of the diffuser tip 223 protrudesfrom the internal tube 117 in the open pool 119. In some embodiments,this protrusion allows a more concentrated amount of electromagneticradiation to penetrate the sealed end 115 of the introducer probe 113.In some embodiments, the open pool provides an area around which coolantcan flow without substantial restriction by the fiber tip 204 (e.g.,blocking and/or restricting coolant flow within the lumens).

In some embodiments, the laser catheter assembly 101 is configured toreceive the optical fiber 202 into the introducer probe 113 via an endaperture 120. In some embodiments, the internal tube 117 is configuredto receive the optical fiber 202 within the second lumen 118. In someembodiments, the optical fiber connector 222 couples with features onthe end aperture 120 to provide a fluid-tight seal. In some embodiments,the coupling fixes the diffuser tip 223 in a position within theintroducer probe 113. In some embodiments, the laser catheter assembly101 receives only one optical fiber 202 and the introducer probe 113 andinternal tube 117 is sized and/or configured to receive only a singleoptical fiber tip 204 and/or diffuser tip 223.

In some embodiments, as noted elsewhere herein, the second lumen 118 isin fluidic communication with the coolant inlet connector 104. In someembodiments, as noted elsewhere herein, the first lumen 116 is influidic communication with the coolant outlet connector 108. In someembodiments, when the optical fiber 202 is positioned within the secondlumen 118, the laser catheter assembly is configured to allow thepassage of a coolant from the coolant inlet connector 104 through thesecond lumen 118 into the first lumen 116 and out of the coolant outletconnector 312.

In some embodiments, the lumen of the laser catheter assembly 101introducer probe 113 can be formed from a material such as nylon, PA12nylon, or a similar material. In some embodiments, PA12 nylon, asopposed to a material such as polycarbonate, advantageously smooths theintroducer probe's 113 passage through introducers and tissue.

In some embodiments, as shown in FIG. 2A, the introducer probe 113comprises printed “hash” marks 121. In some embodiments, the introducerprobe 113 is graduated. In some embodiments, hash marks and/orgraduations can clearly mark the depth of penetration of the probe intotissue (and/or the distance the probe has been withdrawn from tissue).In some embodiments, the hash marks are distanced equal to or less than:about 4 mm apart, about 8 mm apart, about 12 mm apart, values betweenthe aforementioned values, or ranges spanning and/or including thosevalues. In some embodiments, alternating hash marks and dots atintervals permit the pullback of the laser catheter assembly 101 throughtissue for multiple treatments with various optical diffusers (e.g, 1 cmdiffusers, 1.8 cm diffusers, etc.), as discussed elsewhere herein. Insome embodiments, these graduations and/or hash marks allow the probedepth to be visualized directly by a user. In some embodiments, thesegraduations and/or hash marks allow for fine control of the location ofthe probe allowing effective and/or controlled ablation of tissue. Insome embodiments, the introducer probe is of a length equal to or lessthan about: 50 cm, 30 cm, 20 cm, 10 cm, values between theaforementioned values, or ranges including and/or spanning those values.

In some embodiments, the optical fiber 202 comprises a diffuser tip. Insome embodiments, the diffuser tip 223 is a portion of the optical fiber202 having radiation scattering features (e.g., topography, bumps,roughenings, dimples, etc.) that encourage and/or allow the radiation(e.g., laser light, photons, radiation) to exit the optical tip indifferent directions (e.g., scatter, diffuse, etc.). In someembodiments, these features are provided as a gradient along thediffuser and are less dense closer to the laser source 203 and denserfarther from the laser source 203. In some embodiments, the densitygradient encourages a substantially even distribution of radiation alongthe entire diffuser tip. In some embodiments, the diffusive portion 223of the optical fiber 202 may be of different lengths. In someembodiments, the diffusive portion of the optical fiber may be of alength equal to or less than about: 50 mm, 30 mm, 18 mm, 10 mm, valuesbetween the aforementioned values, or ranges including and/or spanningthose values. In some embodiments, the longer diffuser permits thetreatment of larger tumor volumes in the same amount of time by using ahigher laser power and distributing it along a longer diffuser. In someembodiments, using the smaller diffusive tip allows less laser power tobe used and allows treatment of smaller sized tumors with greaterspecificity. In some embodiments, a single treatment can use varioussizes of diffusers to tailor treatment to specific areas of the body andtowards specific tumor dimensions. In some embodiments, as shown in FIG.3B, the optical fiber is supple and/or flexible and is configured tomove within the introducer probe without kinking or cracking. In someembodiments, the optical fiber has a length sufficient to allow thelaser source to be placed out of the way during an operation. In someembodiments, the length of the optical fiber is that is equal to or lessthan: 1 m, 2 m, 3 m, 5 m, or ranges including and/or spanning theaforementioned values.

To illustrate one or more improvements achieved using design features ofthe disclosed laser catheter assembly, the following exemplaryillustration is provided. In some embodiments, hash marks located alongthe introducer probe enable a user to determine the location of thelaser catheter diffuser tip and the extent of treatment to a tumor beingtargeted. In some embodiments, the initial positioning of the introducerprobe (e.g., depth to be inserted into the body along a z-axis andlateral positioning along the x and y axes) can be determined usingComputer Tomography. Once the initial position is reached, the hashmarks can be used to pinpoint treatment locations. The probe can bewithdrawn from one position to the next at set spacings determined bythe graduations on the probe. The printing on the laser catheterassembly provides a “depth gauge” for the user to know how far the lasercatheter assembly has penetrated into tissue or how far the probe hasbeen withdrawn from a starting position. In some embodiments, forexample, 8 mm spacing between hash marks and the 8 mm spacing between“dots” halfway between the hash marks provide a 4 mm spaced “ruler” topermit accurate “pullback”. In some embodiments, as described elsewhereherein, a grid is used to aid in proper positioning of the diffuser tipof the laser catheter assembly within tissue laterally. In someembodiments, as disclosed elsewhere herein, an 8 mm pullback against a10 mm grid permit is used. These markings provide a straightforward wayfor the user to know how deep the laser catheter is situated in thetarget tumor or tissue and to provide a straightforward means ofincrementally pulling back on the catheter in order to produce acontiguous zone of ablation along the catheter track.

In some embodiments, as shown in FIG. 3A and 3B, the optical fiber cancomprise an optical fiber connector 122 (e.g., a luer connector, whichin some embodiments can include an ISO 594-compliant luer taper). Insome embodiments, the optical fiber connector is bonded at a fixeddistance from the distal end of the optical fiber tip 204. In someembodiments, the optical fiber connector 122 is configured to engagewith the end aperture 120 of the laser catheter assembly 101. In someembodiments, the fixed positioning of the optical fiber connector 122can ensure proper setback of the diffuser tip within the laser catheterassembly 101. In some embodiments, fixing the optical fiber 202 withinthe laser catheter assembly 101 can help prevent melting of the tip andcan ensure proper coolant flow around the diffuser. In some embodiments,fixing the optical fiber can help prevent the diffuser tip from slidingout of the laser catheter assembly 101. In some embodiments, fixing theoptical fiber 202 within the laser catheter assembly 101 can help ensurethat the laser diffuses properly out of the diffuser tip (e.g., bypreventing a portion of the diffuser from exiting the inner internaltube 117 or preventing the diffuser from bottoming out against the probe113 tip where it could, for example, occlude the flow of coolant and/orcause uneven distribution of light emitted). In some embodiments, fixingthe fiber can also advantageously provide sufficient diffusion of lightfrom the tip of the introducer probe 113 allowing treatment of thetissue in front of the tip (in addition to tissue laterally adjacent tothe diffuser tip).

In some embodiments, the optical fiber has a total length in meters ofless than or equal to about: 2, 3.5, 5, or ranges including and/orspanning the aforementioned values. This length advantageously lessensclutter in the operating room given that, in some embodiments, theentire laser illuminating system as disclosed herein can be of a sizethat allows it to be housed entirely in the operating room (e.g., in asterile environment).

In some embodiments, the coolant supply system of the laser illuminatingsystem 100 comprises the coolant reservoir 305, the coolant inletconduit 306, and the coolant pump 307. In some embodiments, the coolantsupply system supplies coolant (e.g., saline, water, etc.) to the lasercatheter assembly 101. In some embodiments, the coolant helps preventearly onset of photocoagulation adjacent to the laser catheter assembly101 introducer probe 113. Early onset photocoagulation coulddetrimentally limit light penetration of laser radiation into tissueand/or nullify the tumor specificity of the optically excitednanoparticles.

FIG. 4 shows an embodiment of coolant inlet conduit 306. In someembodiments, the length of the coolant inlet conduit 306 can be lessthan or equal to: about 3 m, about 4 m, about 5 m, about 10 m, valuesbetween the aforementioned values, or ranges spanning and/or includingthose values. In some embodiments, the length of the coolant inletconduit 306 reduces clutter in the operating setting. In someembodiments, the coolant inlet conduit 306 is composed of flexible Tygontubing (polyvinyl chloride tubing or the like, e.g., a flexible tubing)enabling it to be clamped into the cooling pump at any location alongits length. In some embodiments, the tubing is about ⅛″ in diameter. Insome embodiments, the diameter of the tubing is less than about: 1/12″,⅛″, ¼″, or ranges including and/or spanning the aforementioned values.In some embodiments, this diameter permits a smaller pump head spacing,greater control of coolant flow rate, and/or greater consistency of flowrate between tubing sets. In some embodiments, this feature removes theneed for an external flow restrictor and meter in the return line. Insome embodiments, this feature permits greater precision in controllingthe low flow (e.g., equal to or less than about 8 mL/min) coolant flowused during certain methods described herein. In some embodiments, theflow rate in mL/min that can be achieved is less than or equal to 2, 4,8, 10, or ranges including and/or spanning the aforementioned values.FIGS. 5A and 5B show an embodiment of a coolant recovery bag. As shownin FIG. 5B, the coolant recovery bag can comprise a flexible length oftubing configured to attach to the laser catheter assembly.

In some embodiments, the coolant supply set design disclosed hereinadvantageously eliminates or reduces the problem of not being able toposition a coolant pump relative to a reservoir that supplies thecoolant. In some embodiments, the coolant supply system can befabricated with a continuous length of tubing, thereby reducing the partcount and complexity. In some embodiments, the use of polyvinyl chloridetubing of the internal diameters disclosed herein advantageously allowscontrolling the low flow (e.g., 8 mL/min) coolant flow.

In some embodiments, the coolant pump 307 has a flow rate adjuster thatcan be calibrated to default to a given speed in order to produce agiven flow rate. In some embodiments, the pump is a peristaltic pump(e.g., Langer BT100-1L). In some embodiments, the pump delivers flowrates in mL/min of less than or equal to about: 0.002, 0.01, 0.1, 1, 20,50, 100, 500, or ranges including and/or spanning the aforementionedvalues. In some embodiments, the coolant pump 307 has quiet operationfeatures and operates at decibel levels equal to or less than about: 10,20, 30, 40, 50, 60, 70, 80, or ranges including and/or spanning theaforementioned values. In some embodiments, the quiet features of thispump are beneficial because the disclosed system can be placed in anoperating room with the patient.

In some embodiments, the pump 307 can be connected an actuating device(e.g., a footswitch, pedal, panel, button). In some embodiments, theactuating device can be turned on or off by a user (e.g., a physician ortechnician operating the pump). In some embodiments, the laser source isconnected to an actuating device (e.g., a footswitch, pedal, panel,button) that can be the same or different from the actuating device thatcontrols the pump. In some embodiments, where the actuating device ofthe pump and the laser source is the same, the actuating device can haveone or more toggle switches (e.g., buttons or panels) that allow theuser to control the flow of coolant through the laser catheter and/or tocontrol the emission of laser by the laser source separately orsimultaneously. In some embodiments, where the laser source and the pumpare to be activated simultaneously, the actuating device can have asingle switch for turning both the laser source and the pump on or offsimultaneously. In some embodiments, where the laser source and the pumpare to be activated separately, the actuator can have different switchesto activate one device at a time.

In some embodiments, the actuator connection allows coolant flow whenthe laser is active and stops coolant flow when inactive. In someembodiments, in addition to reducing the volume of coolant consumed(e.g., the number of coolant bag changes, etc.), this feature canadvantageously prevent pre-cooling of the tissue between lasertreatments. In some embodiments, the pump is programmable to have adefault flow rate when the laser is in operation. In some embodiments,control of the default flow rate of the pump is helpful for thedisclosed methods which can use of a nominally sub-ablative laser dosewithout using real-time temperature monitoring. In some embodiments, thedefault flow rate in mL/min is less than or equal to about: 0.002, 0.01,0.1, 1, 5, or ranges including and/or spanning the aforementionedvalues. The predetermined flow rate allows the user to remove heat at apre-determined rate. In some embodiments, the automatic stopping ofcoolant flow when the laser is off helps avoid chilling tissue. Flowingcoolant through the laser catheter assembly between laser treatments(e.g., when the laser is off) chills the surrounding tissue (e.g., fromat or around 30-37° C.) to the temperature of the coolant (e.g., at oraround 21-23° C.). In some embodiments, this has the effect of producingunder-treatment because of the additional temperature gradient that mustbe overcome in order to produce tissue ablation. In some embodiments,combinations of the disclosed features allow the cooling to be tightlyregulated. In some embodiments, this temperature control canadvantageously delay tissue coagulation adjacent to the laser catheteruntil the end of the timed treatment. In some embodiments, since theincrease in optical scatter that arises from coagulation effectivelyattenuates optical penetration into tissue, the delay ofphotocoagulation is can aid in treating tumor tissue at longer distancesfrom the laser catheter since nanoparticles are activated only byoptical photons.

In some embodiments, the coolant recovery bag 309 collects the coolantafter a single pass through the laser catheter assembly 101. In someembodiments, the coolant recovery bag 309 is connected to the lasercatheter assembly 101 via a coolant outlet conduit 311 and an outletconduit connector 324 (see FIGS. 5A-B). In some embodiments, the coolantrecovery bag 309 volume is greater than or equal to about 1.5 liters,2.0 liters, or 3 liters. In some embodiments, this volume allows for thecollection throughout the duration of treatment. In some embodiments thetreatment duration is equal to or at least about 62 standard 3-minutetreatments at 8 mL/min using the footswitch activated pump. In someembodiments, the coolant recovery bag 309 has an integrated 1.5 metertubing set, which permits it to be placed at the bedside.

In some embodiments, the laser catheter assembly is introduced into atumor or an organ comprising tumor tissue using a trocar assembly 400comprising a trocar 425 with a sleeve catheter 426 (a catheter sheath)sheathed around the trocar 425. As shown, in FIG. 2B, in someembodiments, the introducer probe 113 is supple and/or flexible (e.g., a25 cm length of probe can be looped into a circle without kinking). Insome embodiments, the tip is comprised of a material that allows flexingwhich advantageously allows the tip to around obstructions at tissues.In some embodiments, as disclosed elsewhere herein, the flexiblematerial of the probe advantageously is resistant to adhesion to tissueand/or is non-stick and/or is substantially non-stick. In someembodiments, the introducer probe 113 has a length (e.g., from theproximal to distal end) of less than or equal to about: 300 mm, 240 mm,200 mm, or ranges including and/or spanning the aforementioned values.In some embodiments, the introducer probe has a width of less than orequal to about: 2 mm, 1 mm, 0.5 mm or ranges including and/or spanningthe aforementioned values.

In some embodiments, to facilitate introduction of the introducer probe113, the introducer probe 113 is inserted into tissue using a trocarsleeve assembly 427 as shown in FIG. 6A-6A2. In some embodiments, asshown in FIG. 6A, the trocar sleeve assembly 427 can comprise the trocar425 and the sleeve catheter 426. In some embodiments, the trocar 425comprises a trocar lumen 428. FIG. 6A1 shows a bisected view of thetrocar assembly 400 with the lumen 428 exposed. FIG. 6A4 shows an end onview of the catheter sleeve assembly 427. FIGS. 6B and 6B1 show thetrocar 425 without the sleeve, where FIG. 6B1 shows a bisected view. Insome embodiments, the trocar 425 also comprises a trocar handle 429, asshown. In some embodiments, the trocar handle 429 is ergonomic. In someembodiments, the trocar handle 429 has one or more finger holds 431 thatfacilitate manipulation of the trocar 425 during placement. In someembodiments, a trocar handle 429 allows placement of the trocar throughtissues of the patient and/or positioning of the trocar assembly 427inside the patient at the site of treatment.

In some embodiments, the trocar 425 comprises a three-sided cannulaand/or needle 430. FIG. 6A3 shows an expanded view of the catheter tip430 with the sheath 426. FIG. 6B2 shows an expanded view of the cathetertip 430 without the sheath 426. FIG. 6B3 shows a front view of thetrocar tip 430. In some embodiments, the three-sided trocar tip 430avoids tissue pull as the trocar is pushed through tissue of a patient.In some embodiments, beveled needles can pull to a side of the bevel asyou pass through tissue. In other embodiments, a beveled needle is usedas a trocar (not pictured). FIG. 6B4 shows an end view of the trocar429.

In some embodiments, after insertion into a site of treatment, thetrocar 425 is removed from the patient's body. In some embodiments, inremoving the trocar 425 the catheter sheath 426 is left inside thepatient. In some embodiments, the catheter sheath 426 can then be usedto position the laser catheter assembly 101 introducer probe 113 intothe site of treatment.

In some embodiments, the methods disclosed herein comprise inserting atrocar assembly 427 comprising a trocar 426 and a catheter sheath 426sheathed around the trocar 426 into a patient at an insertion point(e.g., a first insertion point). Such an insertion is illustrated in thedrawings of FIGS. 7A-J using a test specimen 700 representing a targettissue (e.g., a tumor, etc.). In this case, the test specimen is a rawchicken breast. The test specimen is used as a model for a tumor or foran organ comprising a tumor. FIG. 7A shows the test specimen and atrocar sleeve assembly 427 within a protective cover 433. FIG. 7B showsthe trocar sleeve assembly 427 removed from the protective cover 433. Asshown in FIG. 7C, in some embodiments, the trocar sleeve assembly 427can be inserted into a proximal side 701 (where proximal is in referenceto the position of the user and/or the insertion point) of the targettissue (e.g., the test specimen 700). In some embodiments, as shown inFIG. 7D, the trocar sleeve assembly 427 is inserted through the body ofthe target tissue to a distal side 702 or substantially distal side ofthe target tissue 700. In some embodiments, the trocar sleeve assemblycan be placed at a position intermediate of the proximal and distal sideof the target tissue. In FIG. 7D, the trocar 425 is visible at thedistal side 702 of the target tissue.

As shown in FIG. 7E, in some embodiments, once the trocar catheterassembly has reached the distal side of the target tissue 702, thetrocar 425 can be removed leaving the catheter sheath 426 in place. Insome embodiments, proper positioning of the trocar sleeve assembly 427can be accomplished using MRI, ultrasound, or other real time imagingmethods (e.g., Computer Tomography).

In some embodiments, as shown in FIG. 7F, the introducer probe 113 ofthe laser catheter assembly 101 can be prepared for insertion into thecatheter sheath. As shown, a radius of irradiation 111 is present aroundthe diffuser tip when the laser is activated. In some embodiments, priorto insertion of the introducer probe 113 into the catheter sheath 426,the optical fiber 202 is positioned inside the laser catheter assembly101. In some embodiments, the optical fiber 202 is fixed in the lasercatheter assembly 101 via engagement of the optical fiber connector 222with the end aperture 220.

In some embodiments, as shown in FIG. 7G, the introducer probe 113 ofthe laser catheter assembly 101 can be inserted into the catheter sheath426. In some embodiments, the catheter sheath 426 comprises an insertionport 432 that facilitates insertion of instruments, such as theintroducer probe 113. In some embodiments, after the introducer probe113 reaches the proper position in the target tissue, the sheath 426 canbe withdrawn slightly towards the proximal side of the target tissue 700exposing the introducer probe 113 and/or the diffuser tip 223. In someembodiments, where the catheter sheath is transparent to the radiationemitted by the laser source, the catheter sheath need not be withdrawnto expose the introducer probe 113. In some embodiments, the graduationsof the introducer probe are visible through the catheter sheath 426 toallow depth of insertion into the patient to be easily visualized duringa procedure.

As shown in FIG. 7G, the laser source can be activated to illuminate thediffuser tip 223 creating an irradiated region 710 of the target tissue700. This first region is irradiated for a defined period of time atwhich point, the catheter sheath 426 and introducer probe 113 can bewithdrawn slightly towards the proximal side 701 and away from thedistal side 702 of the target tissue 700 exposing a second region (asecond irradiated region 712) of the target tissue to treatment. In someembodiments, the withdraw/irradiate process can be repeated multipletimes depending on the size of the target tissue. As shown in FIG. 7I,in some embodiments, a third region (third irradiate position 712) canbe irradiated, and so on. In some embodiments, the hash marks 121 of thelaser catheter assembly 101 allow the user to determine the properposition for the first, second, third, fourth, etc. regions forirradiation as the introducer probe 113 is withdrawn.

In some embodiments, the introducer probe 113 and/or the introducerprobe and the catheter sheath 426 are withdrawn from the target tissueincrementally at distances of equal to or less than: about 4 mm, about 8mm, about 12 mm, values between the aforementioned values, or rangesspanning and/or including those values. In some embodiments, thedistance between irradiated regions of the target tissue are equal to orless than: about 4 mm apart, about 8 mm apart, about 12 mm apart, valuesbetween the aforementioned values, or ranges spanning and/or includingthose values. In some embodiments, the distance between irradiatedregions is determined using graduations on the introducer probe. In someembodiments, the trocar sleeve assembly 427 can be reinserted intoanother region of the target tissue (for example, a laterally disposedsecond insertion point) and the above irradiation and withdrawal processcan be repeated. In some embodiments, the laser assembly is repositionedinto different areas of a tumor after irradiation.

In some embodiments, as for the test sample shown in FIGS. 7A-7J, themethod of treating a tumor or tumors in a target region (e.g., a tumorin an organ or gland) can include a step for positioning the trocarsleeve assembly 427 in a patient. In some embodiments, the trocar sleeveassembly is positioned by passing the trocar assembly through, forexample, a prostate tumor such that the trocar assembly passes through aproximal face of the tumor (toward the user who is inserting the trocarsleeve assembly) and terminates at a distal side of the tumor (away fromthe user who is inserting the trocar sleeve assembly). In someembodiments, the insertion of the trocar sleeve assembly from theproximal to the distal side of the tumor and creates a first path withinthe tumor. In some embodiments, as described with the test specimen ofFIGS. 7A-7J, the method of treating a tumor can include a step forremoving the trocar from the patient and leaving the catheter (e.g., thecatheter sheath 426) in the patient within the first path. In someembodiments, a laser catheter assembly 101 (e.g., a laser illuminatorassembly) can be acquired. In some embodiments, as discussed elsewhereherein, the laser catheter assembly 101 can comprise one or more of anintroducer probe 113 and an optical fiber 202. In some embodiments, theintroducer probe 113 (e.g., the laser introducer probe) comprises afirst lumen and terminates in a sealed domed end configured to allowlaser light transmission. In some embodiments, the introducer probecomprises an internal tube located within the first lumen of theintroducer probe. In some embodiments, the internal tube comprises asecond lumen. In some embodiments, the optical fiber can be positionedwithin the second lumen. In some embodiments, when positioned within thesecond lumen, the optical fiber can transmit laser radiation through thedomed end of the introducer probe. In some embodiments, the first lumenis in fluidic communication with the second lumen when the optical fiberis positioned within the first lumen.

In some embodiments, the method includes a step for inserting the laserilluminator assembly into the catheter sheath 426 and guiding the laserilluminator (e.g., the laser catheter assembly 101) to a first positionwithin the first path in the tumor. In some embodiments, the firstposition is located near or at the distal side of the tumor. In someembodiments, the catheter can be partially removed to expose theintroducer probe, or removed completely. In some embodiments, the methodincludes a step of activating the laser illuminator at the firstposition within the first path to generate non-ablative infraredradiation for a first period of time thereby heating the nanoparticlesto an ablative temperature.

In some embodiments, the method includes a step for withdrawing thecatheter and the laser illuminator to a second position within the firstpath. In some embodiments, the second position within the first path iscloser to the proximal side of the tumor than the first position in thefirst path. In some embodiments, the laser illuminator is activated atthe second position within the first path to generate non-ablativeinfrared radiation for a second period of time. In some embodiments, theillumination of the laser illuminator heats the nanoparticles to anablative temperature.

In some embodiments, the method comprises withdrawing the catheter andthe laser illuminator from the first path and inserting the trocarassembly into the patient at a second insertion point. In someembodiments, the second insertion point is laterally disposed on theproximal side of the tumor from the first insertion point. In someembodiments, the trocar assembly is positioned in the patient by passingthe trocar assembly through the prostate tumor such that the trocarassembly passes through the proximal face of the tumor and terminates atthe distal side of the tumor thereby creating a second path through thetumor. In some embodiments, the trocar is removed from the trocarassembly. In some embodiments, the introducer probe of the laserilluminator assembly is then positioned into the catheter. In someembodiments, the introducer probe is guided into place at a firstposition within the second path in the tumor. The catheter can bepartially removed to expose the introducer probe, or removed completely.In some embodiments, the first position is located near the distal sideof the tumor. In some embodiments the first position in any pathwaycould, alternatively, be intermediate between the proximal and distalfaces of the target tissue (e.g., tumor).

In some embodiments, the laser illuminator is activated at the firstposition within the second path to generate non-ablative infraredradiation for a third period. In some embodiments, the activation of thelaser illuminator at the first position of the second path heats thenanoparticles to an ablative temperature. In some embodiments, similarto the procedure used in the first path, the laser illuminator can bewithdrawn proximally to a second position within the second path. Insome embodiments, the laser illuminator can be activated at the secondposition within the second path to generate non-ablative infraredradiation for a fourth period of time thereby heating the nanoparticlesto an ablative temperature.

In some embodiments, the laser illuminator is positioned at 1, 2, 3, 4,5, 6, or more positions for illumination within each pathway. In someembodiments, the distance between irradiated regions of the targettissue within a pathway are equal to or less than: about 4 mm apart,about 8 mm apart, about 12 mm apart, values between the aforementionedvalues, or ranges spanning and/or including those values. In someembodiments, the period of time that the laser is active (e.g., theirradiation time) at each position in a pathway is equal to or at leastabout 1 minute, 3 minutes, 5 minutes, values between the aforementionedvalues, or ranges spanning and/or including those values.

In some embodiments, the irradiate and/or treat and withdraw methodhelps prevent seeding agents (e.g., cancer cells, etc.) along the pathof the treatment. In some embodiments, the catheter sheath 426 can bewithdrawn from the target tissue after placement of the introducer probe113 at the distal target site. In some embodiments, the withdrawingmethod also helps cauterize tissue to prevent bleeding as theinstruments are withdrawn. In some embodiments, by withdrawing the lasercatheter assembly from the distal to the proximal side of the targettissue, blood can be coagulated and/or any bleeding can be substantiallyor entirely sealed-off. In some embodiments, by withdrawing the lasercatheter assembly from the distal to the proximal side of the targettissue, the spread of tumor cells by blood flow, or push through ofcancer cells out of the target tissue, etc.

In some embodiments, the insert and withdraw methods and/or othermethods disclosed elsewhere herein can be performed on tumor tissues, onglands comprising cancer tissue, on organs comprising cancer tissue,and/or on structures (e.g., the throat) comprising cancer tissue. Forinstance, when treating the prostate gland, the introducer probe can beinserted through the prostate to a distal side and withdrawn asdescribed elsewhere herein.

In some embodiments, as described elsewhere herein, a grid or templateis used to determine the insertion points for the trocar sleeve assemblyinto the target tissue (e.g., tumor). In some embodiments, the templategrid with laterally spaced apart holes is used to guide the trocarsleeve assembly placement. In some embodiments, each insertion pointwithin the tissue of the patient is determined by the spacing of theholes in the template grid. In some embodiments, the lateral distancebetween insertion points determined by the template grid is equal to orless than: about 4 mm apart, about 8 mm apart, about 12 mm apart, valuesbetween the aforementioned values, or ranges spanning and/or includingthose values. In some embodiments, the lateral distance betweeninsertion points is not determined using a template grid. In someembodiments, the lateral distance between insertion points is equal toor less than: about 4 mm apart, about 8 mm apart, about 12 mm apart,values between the aforementioned values, or ranges spanning and/orincluding those values. In some embodiments, multiple insertions (e.g.,of multiple probes from multiple laser catheters) can be performedsimultaneously using a grid. In some embodiments, the insertions can beperformed serially using a single laser catheter and a grid.

In some embodiments, because infrared light can penetrate approximately4 mm laterally from the introducer probe, for tumors or treatment areashaving lateral widths greater than 8 mm, multiple insertions of a lasercatheter assembly laser introducer probe (or probes) are used. Whenmultiple insertion points are used, freehanded placement of laserintroducers (or placement using, for example, a ruler to try andmaintain spacing between laser dosing) can result in improper placementof the laser catheter assembly. The likelihood for improper placementcan be high for intra-cavity treatments because it may only be possibleto set the separation of the laser catheter assembly at the skinsurface. In some embodiments, for tumors or treatment areas havinglateral dimensions of greater than 8 mm, a device for positioningmultiple laser catheter assemblies simultaneously (or repeatedindividual placements of a single laser catheter assembly) can be usedto maintain a fixed separation between penetration points. In someembodiments, this device can be a type of template (e.g., a grid orjig).

In some embodiments, a grid template as shown in FIG. 8A can be used toset and/or position laser catheter assemblies at selected separationsand/or to maintain parallel alignment of multiple penetrations of lasercatheter assembly introducer probes. In some embodiments, use of a gridhelps prevent or lessen the amount of untreated margins of a tumor thatcan occur where the laser dose has been inadequate for particleactivation, for example, because of improper probe placement. In someembodiments, the grid comprises a plurality of apertures 801. In someembodiments, each grid aperture 801 is configured to receive a sheathedtrocar 425, a catheter sheath 426, and/or an introducer probe 113. Insome embodiments, once the trocar 425 is placed in the target tissue, itis removed leaving the catheter sheath 426. The introducer probe 113 ofthe laser catheter assembly 101 can then be inserted into the sheath 426and the method of irradiation as disclosed elsewhere herein can beperformed. In some embodiments, as described elsewhere herein, aplurality (2, 3, 4, 5, 6, 7, 8, 9, 10, or more) laser catheterassemblies 101 and introducer probes 113 can be inserted into aplurality of sheaths 426 positioned using a grid. Then, the introducerprobes 113 can be withdrawn together or serially during treatment(thereby shortening the time it takes to treat a target area). In someembodiments, a guidewire can be used. In some embodiments, a guidewireis not used to position the laser catheter assembly.

In some embodiments, hexagonal grids 802 are used as shown in FIG. 8A.In some embodiments, hexagonal grids 802 can be used to provideequidistant spacing to nearest neighbor probes. A square configurationgrid 850 is shown in FIG. 8B. As shown, the grid apertures 851 of thesquare configuration grid 850 align to provide a square shape 852. Asnoted in FIGS. 8A and 8B, labeled markers 803, 804, 853, 854 can be usedto indicate where a laser catheter should be placed within the grid 800,850. As shown in FIGS. 8A and 8B, the labeled markers can comprisealphabetical indicators 803, 853 (e.g., A, B, C, D, E, F, G, H, I, J, K,L, M, N, O, P, Q, R, S, T, U, V, W, X, Y, Z, AA, etc.) or numericindicators 804, 854 (e.g., 1, 2, 3, 4, 5, etc.) on different axes of thegrid. Other indicators can be used, such as colors (e.g., red, orange,yellow, green, cyan, blue, indigo, violet, purple, magenta, pink, brown,white, gray, black), shapes (squares, circles, triangles, diamonds,pentagons, hexagons), or mixtures of color-coded shapes.

While square grids, as shown in FIG. 8B, permit straightforwardidentification of grid positions, they suffer from certain drawbacks asshown in FIGS. 8C and 8D. FIG. 8C depicts a hexagonal embodiment with aminimum aperture spacing of 7 mm. FIG. 8D shows a square configurationwith an aperture spacing of 3 mm. Firstly, for square grids having 3 mmspacings (as shown in FIG. 8D), for example, the grid positions are 3 mmapart in both axes. This means that translation along a diagonalrepresents a translation of 4.24 mm as shown in FIG. 8D. Thus, in orderto completely cover the lateral extent of a tumor for which the opticalpenetration radius is 4 mm, a square grid requires “over-sampling”. Thatis, for a 3 mm square grid, alternate grid positions should be usedalong the principal axes, but along a diagonal there will be a potentialuntreated zone unless each diagonal grid position is used. This is turnleads to time-consuming treatment planning to calculate what gridpositions must be used to completely cover the target area, and whichpositions can be bypassed. As shown in FIG. 8D, a square pattern of 9grid positions with a 3 mm spacing showing the non-overlapping region(white) if a lateral position is not filled.

In some embodiments, the adoption of a hexagonal grid arrangement, aportion of which is shown in FIG. 8C, obviates these difficultiesbecause each nearest neighbor position is equidistant. In someembodiments, once the boundary of the treatment zone is defined, thenall of the interior grid positions are used, completely covering thetarget zone with minimal overlap. This leads to the dual advantage ofdecreasing the number (and/or minimizing) of introducer penetrationsinto the patient and decreasing the number (and/or minimizing) thetreatment time. In some embodiments, a 7 mm spacing between gridapertures can be used to assure a maximum of 4 mm distance from any gridposition. FIG. 8C shows 3 grid positions with a 7 mm spacing showing theconvergence of the 4 mm radius treatment zones. As seen in FIG. 8C, insome embodiments, the maximum distance, at the center of each triad ofholes is set at 4 mm. As a consequence, using adjacent holes for laserplacement assures continuous coverage of a region with minimalredundancy, permitting the most efficient use of treatment time. In someembodiments, the spacing between adjacent grid apertures is less than orequal to about: 5 mm, 4 mm, 3 mm, 2 mm, values between theaforementioned values, or ranges spanning those values.

In some embodiments, the grid is prepared using a monolithicconstruction (e.g., a one piece design). In some embodiments, the gridis machined by computer numerical controlled milling from a single pieceof plastic. In some embodiments, lettering and numbering (e.g.,indicators) are etched into the plastic and/or printed onto the surface.In some embodiments, a monolithic design is distinct from the 3-piecetemplate grids shown in FIG. 8E. In some embodiments, the apertures sizeis less than or equal to about: 20 gauge, 14 gauge, 12 gauge, valuesbetween the aforementioned values, or ranges spanning those values.

In some embodiments, each number and letter designation in a square gridcovers two holes, both vertically and horizontally, leading to atwo-fold ambiguity in both axes for a given callout. In someembodiments, a 7 mm spacing of the hexagonal grid (as shown in FIG. 8A)permits unambiguous identification for every position as well as printedor inscribed horizontal lines on alternate rows of holes in order tofacilitate accurate identification. Drawings of embodiments of ahexagonal grid and a square grid are shown in FIGS. 8F and 8G,respectively.

In some embodiments, during the treatment the laser illuminator can beactivated by an actuator that is controlled by a user. In someembodiments, when the user activates the laser illuminator using theactuator, coolant automatically flows into the first inlet of the laserilluminator assembly. In some embodiments, when the laser illuminator isnot active and not irradiating a tissue, coolant does not flow into thelaser illuminator assembly. In some embodiments, the actuator is a footpedal.

In some embodiments, as discussed elsewhere herein, laser power isabsorbed by nanoparticles within a tissue. In some embodiments, uponabsorption, the nanoparticle heat to sufficiently high temperatures toinduce photothermal coagulation of tissue. In some embodiments,photothermal therapy using nanoparticles can be performed using a laserthat is of sufficiently low power so that it does not in and of itselfinduce coagulative hyperthermia (e.g., 3.5-4.5 W/cm of diffuser). Insome embodiments, the power of the laser is less than or equal to about:2 W/cm, 3 W/cm, 4 W/cm, 5 W/cm, 6 W/cm, or ranges spanning and/orincluding those values. In some embodiments, coagulative hyperthermiaoccurs when the nanoparticles absorb the radiative energy. In someembodiments, non-coagulative hyperthermia can be induced at atemperature below about 45° C., about 35° C., about 30° C., or rangesspanning and/or including those values. In some embodiments, coagulativetemperatures include tissue temperatures equal to or greater than about45° C. In some embodiments, the laser can be activated for a period ofabout 3 to about 5 minutes without inducing temperatures that causephotothermal coagulation.

In some embodiments, the laser illuminator emits radiation having a nearinfrared wavelength. In some embodiments, the nanoparticles can bedesigned to have light absorption maxima in radiation in thenear-infrared region (e.g. ranging from about 670 nm to about 1200 nmwavelengths) that allow the penetration of this energy through normaltissue. In some embodiments, upon the application of a laser emittingwithin these wavelengths, the nanoparticles absorb and convert thisenergy into heat to elevate the temperature of the tumor to an ablativelevel. In some embodiments, the effect of the nanoparticle-inducedhyperthermia is to create a temperature elevation confined to the tumorand the region immediately adjacent thereto, localizing the area oftissue ablation and reducing damage on surrounding healthy tissue. Insome embodiments, the laser illuminator emits radiation having a nearinfrared wavelength ranging from about 805 nm to about 810 nm. In someembodiments, a wavelength of about 805 to about 810 nm allows lowerabsorption by tissue (and hemoglobin), while increasing the absorptionof the nanoparticles. In some embodiments, a wavelength of about 1000 nmcan be used.

In some embodiments, the laser illuminator emits radiation that is ofinsufficient power to induce photothermal coagulation of tissue. In someembodiments, the optical fiber comprises a diffuser tip that distributesthe non-ablative infrared radiation within the tumor. In someembodiments, the laser illuminator emits radiation between about 3.5W/cm and about 4.5 W/cm of the diffuser tip.

Some embodiments pertain to kits for use in laser therapy as describedelsewhere herein. FIGS. 9A-9G show an embodiment of a kit, which cancomprise one or more components of the laser illuminating system. Insome embodiments, as shown in FIG. 9A a container with packing materialcan be provided. In some embodiments, the kit comprises an opticaldiffuser pack as shown in FIG. 9B. In some embodiments, the opticaldiffuser pack comprises an optical fiber 202 with an optical fiber tipand an optical fiber connector as described elsewhere herein. In someembodiments, the optical diffuser pack comprises a optical fiber sheaththat protects the fiber and/or the diffuser tip. In some embodiments,the kit comprises a coolant supply set as shown in FIG. 9C. In someembodiments, the coolant supply set comprises one or more of a coolantreservoir, a coolant inlet conduit, an inlet conduit connector, acoolant recovery bag, a coolant outlet conduit, and/or a coolant outletconnector. In some embodiments, the kit comprises a laser catheterassembly packet. In some embodiments, the laser catheter assembly kitcomprises one or more of a laser catheter assembly 101. In someembodiments, the introducer probe 113 of the laser catheter assembly isprotected using a protective sheath 122 as shown in FIG. 9D. In someembodiments, the further comprises instructions 910 (e.g., on theassembly or use of the laser catheter assembly) shown in FIG. 9E. Insome embodiments, the instructions may comprise drawings such as thoseshown in FIG. 1. In some embodiments, the method for using the lasercatheter system as disclosed elsewhere herein is provided as part of theinstructions. In some embodiments, as shown in FIG. 9F, an additionallayer of packing material is used to cover the kit. In some embodiments,as shown in FIG. 9G, the packing container can be closed and sealed toprovide a kit that is ready to ship. While not shown, in someembodiments, the kit may further comprise the coolant pump, the trocarand devices related there to, the grid assembly, etc. Additionally, oneor more of the components shown in FIGS. 9A-9G can be excluded from thekit.

Some embodiments have been described in connection with the accompanyingdrawings. Some of the figures are drawn to scale, but such scale shouldnot be limiting, since dimensions and proportions other than what areshown are contemplated and are within the scope of the disclosedinvention. Distances, angles, etc. are merely illustrative and do notnecessarily bear an exact relationship to actual dimensions and layoutof the devices illustrated. Components can be added, removed, and/orrearranged. Further, the disclosure herein of any particular feature,aspect, method, property, characteristic, quality, attribute, element,or the like in connection with various embodiments can be used in allother embodiments set forth herein. Additionally, it will be recognizedthat any methods described herein may be practiced using any devicesuitable for performing the recited steps.

EXAMPLES Example 1 Laser Catheter Testing

It has been observed that certain laser introducer probe tips of cooledcatheter laser systems melt during clinical procedures and result in theformation of char on the tips with the consequent loss of lightpenetration into tissue. This char also results in non-specificcoagulation and thermal fixation. The heating of the embodiments havinga domed laser catheter tip was compared side-by-side to a Visualase®Cooled Catheter System (CCS) (having a ground conical tip). It wasdetermined that the conical tip of the CCS created a significant focusof heat, greatly exceeding that of the domed laser catheter tip. Theexperiments described in this example show that the heating of the CCSis concentrated in the conical tip and that from one-third to overone-half of this heating is the result of end losses from the laserdiffusing fiber (LDF). This conclusion was reached by using both theVisualase Laser Diffusing Fiber and embodiments having a domed lasercatheter tip in the same conical Visualase Cooled Catheter System underthe same conditions. When the embodiments having a domed laser cathetertip was used, the evolved heat was 34-57% less than when the VisualaseLDF was used in the same Visualase conical-tipped catheter. Withoutbeing bound to a particular theory, the excess light leakage out of theend of the Visualase LDF and the conical catheter tip itself bothcontribute to the development of a device-destroying hot spot. Theremainder of tip heating results from the shape and material of thecatheter itself. In contrast to the 22-57° C. temperature rise using aCCS, the temperature rise in a domed laser catheter tip under similarexperimental conditions was less than 2° C.

Test Organization

The Visualase CCS and a laser catheter assembly comprising a domed lasercatheter tip were configured similarly to each other, with an isotropicdiffuser tipped optical fiber secured within a transparent, dual lumen,liquid-cooled 16G catheter. Tests were performed in open airrepresenting a “worst case scenario” in that there is no thermalcoupling and/or heat transfer to tissue, which would tend to aid in thedissipation of heat away from the tip. The CCS was assembled as part ofa standard Visualase Cooled Laser Applicator System (VCLAS). The tip ofthe 11 meter LDF was advanced to within 2 mm of the terminus of the CCStip. The coolant inlet and outlet were supplied with a VCLAS tubing set(not including the extension set) supplied from a 1 L flask of roomtemperature water. Coolant was supplied by a Visualase K-Pump.

The experimental layout for the experiments performed is shownpictorially in FIGS. 10A and 10B. The coolant pump 307 and laser 203were placed on a cart (at left of FIG. 10A) and were connected to theCCS/LDF assembly 901 via a coolant tubing set. A thermal camera 900, thesmall object mounted to the adjustable arm at the center of both FIGS.10A and 10B, was operated from a laptop computer. A power source 902 isalso shown. The CCS/LDF assembly is suspended on the ring stand shown inFIG. 10B. The laser power meter is at the right in the FIG. 10A.

Tests

1. Heating of the CCS/LDF assembly 4.5, 6.0, and 12.0 W laser power,measured in air, with nominal coolant flow.

2. Heating of the CCS assembly with an 18 mm AuroLase Optical FiberDiffuser substituted for the Visualase LDF.

Test Conditions

Air: non-physiological condition that permits ready measurement by athermal camera, and which represents a “worst case scenario” for thermalconductivity;

Orientation: in all cases the CCS assembly 901 was mounted verticallywith the tip downward;

Laser output: 4.5±0.1 W for 10 mm diffuser, 6.0±0.1 W for 18 mmdiffuser, and 12.0±0.1 W, 2× standard laser power (and near the maximumavailable laser output);

Nominal coolant flow: 7.9±0.2 mL/min water at room temperature (20-21°C.).

CCS Experimental Setup

Laser: Diomed 15+ #10000126

Coolant pump: Visualase K-pump, property #10000125

Coolant supply: standard AuroLase Therapy CSS

Optical power optometer: Gigahertz-Optik P9710-2, NBI property#10000242/243

Thermal camera 900: ICI model 3720.

Data recording and image control software: Lenovo Ultrabook Yoga 2 prorunning custom ICA IRFlash application

Test Articles

The Cooled Catheter Assembly with Laser Diffusing Fiber advanced to 2 mmfrom catheter tip;

Cooled Catheter Assembly with 18 mm Optical Fiber Diffuser advanced to 2mm from catheter tip.

Heating of the CCS/LDF assembly

FIGS. 11A and 11B show the data for a Visualase® Cooled Catheter System(CCS) (having a ground conical tip; FIG. 11A) and for a domed lasercatheter tip as disclosed elsewhere herein (FIG. 11B). FIG. 11A showsthe increase in peak temperature of the distal end of the CCS assemblyover 3 minutes of 4.5, 6.0, and 12.0 W of laser output. The coolant flowwas un-interrupted and set at 7.9 mL/min sourced from a room temperature(20° C.) 1 liter reservoir. The temperatures followed a characteristicfirst order transient response. At 4.5 W the temperature rose 22°, at6.0W the rise was 28° C., and at 12.0 W the rise was 57° C. Settling atthe final temperature was rapid, with a time constant of 1.9-2.9seconds, effectively coming to equilibrium within 15 seconds in allcases.

FIG. 11B shows the heating of the laser catheter assembly comprising adomed laser catheter tip under heating conditions coinciding to those ofprevious irradiation of the Visualase system in FIG. 11A. By comparison,for the laser catheter assembly comprising a domed laser catheter tip at12.0 W irradiation, the temperature rose 1.2-1.6° C. above ambienttemperature during the course of a standard 3-minute treatment. FIG. 11Bshows heating of the laser catheter assembly comprising a domed lasercatheter tip under nominal (6.0 W/18 mm diffuser) and 2× laser outputfor both Assembly #1 (circles) and Assembly #2 (squares). Assemblies #1and #2 are two identical optical fiber/laser catheter assemblies thatwere tested under identical conditions. The assemblies were cooled at8.0 mL/min with room temperature water. FIGS. 11A and 11B are scaleddifferently in order to clearly show the temperature evolution indetail. For instance, FIG. 11B shows an expanded view of thetemperature.

FIGS. 12A and 12B show false-color thermal images of the distal end 950of the CCS/LDF assembly and the end of the 6.0 W irradiation. FIGS. 12Cand 12D show false-color thermal images of the distal end of anembodiment of a domed catheter at the end of the 6.0 W irradiation. Heatis concentrated at the very tip of the CCS, which is 52.4° C., or 28°above ambient. FIG. 12B shows a close-up of the CCS/LDF tip under 6.0 Wirradiation clearly showing heat buildup at the extreme end of theconical tip. From FIG. 12A, it is immediately apparent and clear thatthe heating is concentrated within the conical tip. This is furtherdemonstrated by the close-up of the CCS tip in FIG. 12B where thehottest portion is seen to be the extreme tip of the CCS. From FIGS. 12Cand 12D it is apparent that heat does not build in the tip of the domedcooled catheter.

2. Heating of the CCS/OFD Assembly

The evolution of heat by the different laser catheters has two sources:the optical fiber diffuser itself and the material and conformation ofthe enclosing catheter. In order to distinguish between these twocontributions an optical fiber diffuser of the laser catheter systemdescribed elsewhere herein was substituted into the CCS and the laserirradiations were repeated.

FIG. 13 shows the increase in temperature of the CCS using an embodimentof a laser diffuser disclosed herein (having an 18 mm diffuser tip)instead of the Visualase Laser Diffusing Fiber. FIG. 13 records theincrease in peak temperature of the distal end of the CCS/OFD assemblyover 3 minutes of 4.5, 6.0, and 12.0 W of laser output. The coolant flowwas un-interrupted and set at 7.9 mL/min sourced from a room temperature(20° C.) 1 liter reservoir. The temperatures also followed acharacteristic first order transient response. At 4.5 W the temperaturerose 9.4°, 12.3° C. at 6.0 W, and 38° C. at 12.0 W. Settling at thefinal temperature was less rapid than previously, with a time constantof 2.2-4.8 seconds, effectively coming to equilibrium within 25 seconds.Overall, the change from the LDF to the OFD reduced the evolved heat by57% for the 4.5 W output, 56% for the 6.0 W output, and 34% for the 12.0W output. Since the heating of the CCS is overwhelmingly in the conicaltip it was concluded that: 1) the 34-57% reduction in heating affordedby switching to an optical diffuser disclosed herein is the result ofgreatly reduced end loss from the diffuser tip, and 2) the appreciableheat is the result of light being focused within the conical tip.

Conclusion

The observed tendency for the conical tips of Cooled Catheter Systems tomelt during clinical procedures results in the formation of char on thetips with the consequent loss of light penetration into tissue and innon-specific coagulation and thermal fixation. The experiments describedherein demonstrate that this heating of the CCS is in fact concentratedin the conical tip, from ⅓ to over ½ of this heating is the result ofend losses from the Laser Diffusing Fiber, and the remainder from theshape and material of the catheter itself. By contrast, with the 22-57°temperature rise in the CCS, the temperature rise using embodiments oflaser catheter assemblies as disclosed herein (e.g., an embodiment asdisclosed herein having a domed tip) under near-identical conditions wasless than 2° C.

Example 2 Treatment of a Prostate Tumor

This is a single-arm study with a single group of patients. An objectiveof the study is to determine the efficacy of using MRI/US fusion imagingtechnology to direct focal ablation of prostate tissue usingnanoparticle-directed laser irradiation.

The patient population consists of men with low to intermediate risklocalized prostate cancer with MRI visible and confirmed focal areas ofprostate cancer using MRI/US Fusion Guided Biopsy. The patient also hasno disease detected via ultrasound guided biopsy outside of areasvisualized on MR imaging.

There is one arm/group to this study: Up to forty five (45) patientsreceive a single intravenous infusion of AuroShell particles 12 to 36hours prior to MRI/US guided laser irradiation using an FDA clearedlaser and an interstitial optical fiber.

Efficacy and acute volume of ablation is assessed by contrast-enhancedMRI 48-96 hours after laser illumination to allow time for theappearance of coagulative necrosis and prior to reconfiguration oftissue by lytic action. An appearance of a ‘void’ on MRI is moregenerally expected than lesion shrinkage.

Efficacy of focal ablation of prostate tissue is assessed byMRI/Ultrasound guided biopsy at 90 days (primary endpoint) and again at1 year after laser treatment. Per standard of care patient follow-up ison a 6 month basis beyond the one year follow up but is outside thescope of the initial study.

Nanoparticle Dose: in this study AuroShells are used. These are goldnanoshells. AuroShell Dose: Each patient receives an infusion of up to7.5 mL/kg of AuroShell particles concentrated to 100 Optical Density(approximately 2.77×10¹¹ particles/mL or 36 mg particles/kg of patientweight). AuroShell particles are administered intravenously through astandard non-DEHP infusion set, and are infused at rates ranging from120 mL/hour to the nominal 600 mL/hour at the investigator's discretion.

Laser Dose: Laser illumination takes place under ultrasound guidance 12to 36 hours after particle infusion. An isotropic fiber in awater-cooled jacket with an isotropic diffusing tip is inserted viatransperineal approach. The urethra is cooled by circulating saline (orwater) through a urethral catheter. Up to 5.0 Watts per cm of opticalfiber diffuser length of measured output of 810±10 nm laser power isdelivered for a period of up to 4 minutes for each treatment site. Ifnecessary, the laser fiber is repositioned and a separate zoneilluminated.

Inclusion Criteria

Patients have documented histological or cytological evidence oftumor(s) of the prostate. Patients are ≥45 years of age. Patients ortheir legal representative are able to read, understand and sign aninformed consent. Organ confined clinical T1C or clinical T2a prostatecancer that is visualized on MR imaging. Prostate cancer is diagnosed byMR image guided biopsies. Gleason Score≤7; and 2 or less positivelesions on prior MR US fusion guided prostate biopsy. If the standardbiopsy cores are positive, they should be from the same location in theprostate as MR lesion was biopsied and proven to be cancerous.(Left/Right, Base, Mid Gland, Apex). Prior MRI results dated within 120days prior to ablation. No metastatic disease as per NCCN guidelines(www.nccn.org)—Bone scan indicated to r/o metastatic disease if clinicalT1 and PSA>20 or T2 and PSA>10 PSA<15 ng/ml or PSA density<0.15 ng/ml2in patients with a PSA>15 ng/ml. The patient has given written informedconsent after the nature of the study and alternative treatment optionshave been explained.

Exclusion Criteria

Patients with known hypersensitivity to any of the components of aPEGylated gold nanoshell suspension (polyethylene glycol, gold).Patients who are receiving concurrent investigational therapy or whohave received investigational therapy within a period of 5 half-lives ofthe investigational therapy in question prior to the day of dosing withthe PEGylated nanoshell particles. Introduction

Prostate cancer is the most commonly diagnosed cancer in men. In 2014,approximately 233,000 men in the United States were diagnosed withprostate cancer and an estimated 29,000 died from the disease. Theaverage annual incidence of prostate cancer among African American menwas 60% higher than among non-Hispanic white men, and the average annualdeath rate was more than twice that of non-Hispanic white men.

Existing treatment modalities for primary prostate cancer include“active surveillance”, surgical resection, and radiation (includingbrachytherapy). These modalities have a significant level of sideeffects, including erectile dysfunction, urinary incontinence, andrectal damage. Focal therapeutic approaches that reduce the adverseeffects associated with treatment, eradicate the current disease, orpotentially increase the time to progression are needed.

The optical properties of tissues inherently limit the depth ofpropagation of optical energy, thereby enabling a truly focal therapy.Heat evolved from an energy source is inherently diffuse andnon-specific. Although thermally ablative heat can be made to propagateon the millimeter scale, it is not specific to tumor conformation.Nanoshell particles offer the opportunity for more precisely localizedconformal therapy and result in tumor specific damage on the millimeterscale.

The MRI fusion imaging approach, using ultrasound guidance based on apriori MRI fusion imaging, should permit the precise placement of theoptical fiber catheter within or adjacent to the prostate lesion(s)targeted for ablation.

A merging of MRI fusion imaging and the subsequent directed placement ofthe laser catheter represents a means of establishing the efficacy andutility of nanoshell therapy for the focal therapy treatment of prostatetissue. The MRI-Ultrasound fusion approach resolves limitationsidentified using an ultrasound only approach; given the ability of MR USfusion technology to allow:

1) pre-treatment target planning, and 2) guided imagery to be used as anadditional level of safety after the initial use of ultrasound forplanning placement of the catheters using a brachytherapy stepper whichallows for the accurate placement of the laser catheter in proximity tothe lesion to be ablated.

The methods can also be used in squamous cell carcinomas of the head andneck, canine melanomas and carcinomas of the oral cavity, and in canineand human prostate all serve to demonstrate the inherently focal natureof particle-directed photothermal energy. Incorporation of an imagingmodality can enable precise lesion treatment. Further, the ability ofparticles to co-locate to neoplastic tissue can further enable lesionablation conformal to the target tumors.

The potential benefit of nanoshell therapy is highly selective and rapidtumor destruction with minimal damage to surrounding tissue enabling apotentially curative treatment of tumors with minimum toxicity.Preclinical studies have demonstrated that nanoshell therapy iseffective and causes no detectable systemic toxicity.

Investigational Devices and Systems

Nanoshells and the laser illuminating system disclosed hereinselectively destroy solid tumors using near infrared illumination from alaser. Unlike other energy-based ablation methods, which rely upon theendogenous absorption and transduction of the deposited energy intoheat, nanoshell particles, delivered systemically to the tumor, serve asan exogenous absorber of this laser illumination to generate a lethalthermal response specific to tumor tissue.

Nanoshell therapy is comprised of three components: (i) a near infraredlaser source, (ii) an interstitial fiber optic probe for delivery of thelaser energy to a site near and/or inside the tumor, and (iii) nanoshellparticles, a near-infrared absorbing inert material designed to absorband convert the laser energy into heat. Nanoshell particles aredelivered systemically, and allowed to accumulate selectively at thetumor site and then illuminated by a near-infrared laser. The particlesabsorb and convert this illumination into heat, resulting in the thermaldestruction of the tumor and the blood vessels supplying it with minimaldamage to surrounding healthy tissue. Since the accumulation of theparticles within the peri-vascular space of tumors is passive anddepends only upon the fenestrated neo-vasculature characteristic ofsolid tumors, nanoshell therapy may be used in patients previouslytreated with chemotherapy and radiation. During the procedure, needlethermocouples placed around the tumor may be used to monitor margins oftreatment. In some embodiments, this will provide monitoring oftemperatures around the ablation zone and permit the operator tominimize the risk of overheating critical structures or areas outside ofthe intended target tissue. Low temperature control points (about 45° C.to about 50° C. threshold) are used near critical structures, such asthe urethra, urinary sphincter and rectal wall, in order to avoid damageto these tissues.

Nanoshell therapy is useful in recurrent and refractory head and neckcancer and metastatic lung tumors.

There is one arm/group to this study. Up to forty five (45) patientsreceive a single intravenous infusion of nanoshell particles 12 to 36hours prior to ultrasound-guided laser irradiation using an FDA clearedlaser and interstitial laser fiber. Acute efficacy and volume ofablation is assessed by contrast-enhanced MRI 48-96 hours following thelaser illumination in order to allow time for the appearance ofcoagulative necrosis but, prior to reconfiguration of tissue by lyticaction. An appearance of a ‘void’ on MRI would be more generallyexpected than lesion shrinkage.

Nanoshell/laser catheter therapy is a system for the photothermalablation of solid tumors using near-infrared energy. The system utilizesan interstitial fiber optic probe to deliver near-infrared energyemitted by an FDA-cleared laser to a site proximate to and/or inside asolid tumor. Unlike other energy-based ablation methods, which rely uponthe endogenous absorption and transduction of the deposited energy intoheat, Nanoshell/laser catheter therapy particles, delivered systemicallyto the tumor, serve as an exogenous absorber of this laser illuminationto generate a lethal thermal response specific to tumor tissue.

Nanoshell/laser catheter therapy is comprised of three components: (i) anear infrared laser source, (ii) an interstitial fiber optic probe fordelivery of the laser energy to a site near and/or inside the tumor, and(iii) nanoshell particles, a near-infrared absorbing inertinvestigational material designed to absorb and convert the laser energyinto heat.

Nanoshell/laser catheter therapy may be used with an FDA-clearedclinical laser that emits near infrared energy with the desiredparameters (energy, duty cycle, cycle time) and with an interstitialfiber optic probe for percutaneous energy delivery. The nanoshellparticles used in this study consist of a gold metallic shell and anon-conducting, or dielectric, core that serves as the exogenousabsorber of the near infrared laser energy delivered by the fiber.

Nanoshell/laser catheter therapy in this study uses an FDA-clearedlaser, either the Diomed 15-PLUS (K013499) or LiteCure, LLC (K093087) asan infrared energy source and an interstitial, liquid-cooled opticalfiber source.

The steps involved in Nanoshell/laser catheter therapy can include oneor more of: (i) the intravenous infusion of a dose of nanoshellparticles, (ii) a time delay of 12 to 36 hours to allow the accumulationof the nanoshell particles within the tumor by the enhanced permeabilityand retention (EPR) effect, and (iii) the illumination of the area withcontinuous wave (CW) or pulsed coherent light at a desired wavelength,for example, between 800 and 815 nm, for up to 4 minutes at up to 5.0Watts average delivered output (assuming a 1-cm long isotropic diffusingdelivery). The nanoshell particles in the area absorb light, and themetal shell converts the absorbed light to heat, generating heatsufficient to thermally ablate the tumor. The applicator can bepositioned externally or inserted interstitially or endoscopically andcan use either a collimated or dispersing fiber tip.

Nanoshell particles used in this study consist of a metallic shell and anon-conducting, or dielectric core. These particles can be designed andconstructed to absorb or scatter light at desired wavelengths. This“tunability” is achieved by altering the ratio of the thickness of themetal shell to the non-conducting core. The exterior shell of theparticle is comprised of gold, which has a long history of use in vivoin particulate form, as an implanted material, or as a coating onimplanted devices. The non-conducting core is silica, but can becomprised of any dielectric material. For cancer therapy, nanoshellparticles are designed to absorb infrared light at wavelengths wherelight is not significantly absorbed by human tissue. Human tissue isminimally absorptive in the ranges from 750 nm to 1100 nm, oftenreferred to as the “water window” or “tissue optical window”. Whilesolid gold nanoparticles and microparticles absorb light at wavelengthsalso absorbed by tissue, gold-coated nanoshell particles can be designedto absorb or scatter light within this “tissue optical window”, enablingnew in vivo applications.

More specifically, the nanoshell particles used in this study arecomprised of a thin gold shell, 10 to 20 nm thick, deposited on a solidsilica (silicon dioxide) core. To prevent aggregation of the particlesin a saline environment and to provide steric hindrance in vivo, a 5,000molecular weight (MW) methoxy-polyethylene glycol (PEG) chain isattached through a thiol (sulphur) bond. The PEG coating improves thestability of the nanoshell particles in an isotonic aqueous solution,and may also improve circulating half-life on administration. For thestudies reported here, the particles are concentrated to a desired level(generally less than 0.1% by volume) and suspended in an isotonicsolution for injection (10% trehalose in water).

Mechanisms of Action

Lasers and radiofrequency ablation devices are used to thermally destroytissue by delivery of energy at a rate in excess of the tissue's abilityto dissipate the energy through blood perfusion thermal diffusion. Inaddition, some lasers provide energy at wavelengths naturally absorbedby chromaphores within tissue or blood, using the properties of tissueor blood as a natural absorber to convert the light to thermal energy.The result is either thermal coagulation of cells or tissue thermalfixation and the disruption of the vasculature.

Nanoshells particles are infused intravenously and are known toaccumulate in tumor stroma as a result of the fenestrated vasculatureassociated with tumors. This method of accumulation has been establishedby other particles and is termed the EPR effect. SEM analysis of tumortissue following nanoshell particle intravenous injections indicatesparticle accumulation is preferentially near the tumor vasculature.

Nanoshell particles are designed to absorb near-infrared energy,transducing it into heat via surface plasmon resonance. Thenear-infrared dose level utilized by Nanoshell/laser catheter therapy isbelow that which would cause significant damage to tumor or normaltissue without the presence of nanoshell particles. In the presence ofnanoshell particles in tissue, the near-infrared dose will generate athermal response that may be sufficient to result in photothermalcoagulation, leading to cell death. It is likely that this to includethe disruption or occlusion of tumor vasculature in a manner similar tothe FDA-cleared embolism microspheres.

Preparation of Nanoshells

The nanoshell particles used in this study are packaged in units of 80mL in a sterile IV bag and maintained at 2 to 8° C. For infusion, thepackage should be removed from refrigeration and allowed to warm to roomtemperature over 30 minutes. The bag should be gently kneaded or shakento ensure the uniform dispersion of the material. The tubing forinfusion should be C-Flex, non-DEHP, medical grade tubing. A 1.2 micronfilter (Pall TNA1 or comparable) should be installed between theinfusion tubing and the patient catheter.

Particle Dose and Administration

The nanoshell particles are infused at a rate of 600 mL/hour (10mL/minute). During the three days prior to and first 6 hours afteradministration, vasoconstrictive medications are avoided to maximizeparticle accumulation in tumor. Each patient receives an intravenousinfusion of up to 7.5 ml/Kg of nanoshell particles concentrated to 100Optical Density (approximately 2.77×10¹¹ particles/mL or 36 mgparticles/kg of patient weight.

Laser Application

Laser illumination will take place under MRI/US fusion guidance 12 to 36hours after particle infusion. The urethra may be cooled by circulatingsaline (or water) through a urethral catheter (typ. 6-10 mL/min). Anoptical fiber with an isotropic diffusing tip in an enclosed catheter isinserted interstitially using a transperineal approach employing 14Gneedle/cannula introducers. Up to 5.0 Watts of measured output of 810±10nm laser power is delivered for a period of up to 4 minutes for eachtreatment site. If necessary, the laser fiber may be repositioned and aseparate zone illuminated.

The specific procedures are described in the Instruction Manual forAuroLase Therapy (IFU), but a summary of the procedure is as follows:

Prior to use, calibrate the laser and verify laser output through thelaser fiber to up to 5.0 Watts/cm average output. Prior to use, verifythat the cooling system for the laser fiber is functioning properly.Using ultrasound guidance, insert needle/cannula introducers into theprostate proximal to the index lesion to be treated, avoiding theurethra and other critical structures. The MRI generated fusion imagesare not used for guidance of the laser placement, but serve only as acheck on the placement via ultrasound guidance. Withdraw the needle fromthe introducer and replace it with the laser catheter. Withdraw thecannula to expose the emitting portion of the laser catheter. Ifindicated by the proximity of the target lesion to a sensitive orcritical structure (e.g., urethra, prostate capsule, or nerve bundle) aneedle thermocouple may be inserted at clinician discretion alongsidethe laser catheter in order to monitor temperatures near the treatmentzone. Position the fiber to illuminate a zone within the prostate for upto 4 minutes. If indicated by the size of the lesion to be treated,withdraw the fiber a distance of 2 mm less than the illumination lengthand illuminate the new zone. Repeat as required to illuminate the entirelesion. If additional target lesions are to be treated, repeat steps atthe new site. If a single target lesion is treated, the investigatorwill make a single laser treatment in the contralateral prostatehemisphere to serve as a negative control of the laser treatment (i.e.,no thermal damage to normal tissue in the absence of the accumulation ofparticles in the perivasculature of tumor tissue). In the event of thetreatment of two lesions with one in each hemisphere of the prostate,this negative control procedure will not be performed. At the discretionof the investigator, if a Foley catheter was used to cool the urethraduring the laser procedure it may remain in order to prevent occlusionof the urethra as a consequence of thermally-induced edema. The Foleycatheter may remain in place until the follow-up MRI on Day 4/5.

Complete physical examination (general appearance, skin, neck, ears,eyes, nose, throat, lungs, heart, abdomen, back, rectal, lymph nodes,extremities, neurological status) is performed at baseline and the 90day follow-up.

A follow up MRI fusion biopsy is taken at the 90 day follow-up visit toassess the efficacy of the tumor ablation with a view to ascertain thepresence of viable cancer cells within the treatment zone and thereforethe efficacy of focal ablation of prostate tissue. The patient has thestandard of care reassessment biopsy at Year 1 and six months thereafterper physician treatment considerations. This includes MRI/US fusionbiopsy and a standard 12 core biopsy.

Results

The patients have an 70-80 percent reduction of tumor size 6 monthsafter therapy. In 25% of the patients, the prostate cancer is completelyeradicated. In 50% of the patients, no side effects are noted and normalprostate function is maintained.

Example 3 Treatment of a Head and Neck Tumors

A Pilot Study of AuroLase Therapy in Patients with Refractory and/orRecurrent Tumors of the Head and Neck.

This is an open-label, multicenter, single-dose pilot study of AuroLaseTherapy in the treatment of patients with refractory and/or recurrenttumors of the head and neck. Three (3) treatment groups of five (5)patients each are enrolled and observed for six (6) months followingtreatment. Each group receives a single dose of AuroShell particles.This dose may be increased by up to 67% for the second and third groupif no significant unanticipated adverse device effects are observed inthe first group. The laser illumination for each group consists of oneor more interstitial illuminations (based on tumor size) with anescalating laser dosimetry for the second and third groups.

The first group of five patients are treated with the lowest treatmentlevel of 4.5 ml/Kg of AuroShell particles concentrated to 100 OpticalDensity (approximately 1.3×10{circumflex over ( )}12 particles/Kg or 20mg particles/Kg). An isotropic fiber in a water-cooled jacket with a onecm diffusing tip is inserted interstitially within and/or proximate tothe tumor and up to 3.5 Watts measured average output of 800-810 nmlaser power is delivered at a 75% duty cycle, 1.25 pulses per second fora period of up to four (4) minutes. The fiber may be repositioned atdistances of 1 cm from the original placement to provide illumination toother sides of the tumor, or different tumors, with appropriateprecautions. For tumors greater than 1.0 cm in estimated thickness atthe point of fiber placement, the fiber may be retracted within thecatheter to provide illumination of the tumor mass.

Following treatment of the first three (3) patients, safety data(including data from the fourth week visit after treatment) for eachpatient is submitted per FDA's request. In the absence of unanticipatedadverse device effects, enrollment and treatment is continued for thetwo additional patients being treated at the lowest concentration of 4.5ml/Kg (totaling (5) patients in the first group of the study). TheAuroShell dose is increased from 4.5 ml/Kg to 7.5 ml/Kg of AuroShellparticles concentrated to 100 Optical Density (approximately2.1×10{circumflex over ( )}12 particles/Kg or 34 mg particles/Kg) forthe second and third group if no unanticipated adverse device effectsrelated to AuroShell dose are observed in the first group.

For the second treatment group of five (5) patients, laser illuminationmay be increased to 4.5 Watts measured average output of 800-810 nmlaser power delivered at a 75% duty cycle, 1.25 pulses per second for aperiod of up to 4 minutes if no unanticipated adverse device effects areobserved in the first group.

For the third treatment group of five (5) patients, laser illuminationmay be increased to 5.0 Watts measured average output of 800-810 nmlaser power delivered at a 100% duty cycle (continuous wave) for aperiod of up to 4 minutes if no unanticipated adverse device effectsattributable to AuroLase Therapy are observed in the second group.

In each treatment group, the AuroShell particles is administeredintravenously at a rate of 2 ml/minute for the first 15 minutes, andthen increased to up to 10 ml/minute. At approximately 0.5, 2, 4, 8, 24and 48 hours following administration of the AuroShell particles, a 2 mlblood sample is obtained and the concentration of the particlesdetermined by dynamic light scattering analysis (DLS) and neutronactivation analysis (NAA).

Approximately 12 to 36 hours after intravenous infusion of theparticles, the target tumor(s) is illuminated by laser as described.Subsequent to the AuroLase treatment of the target lesions, biopsies isperformed and the gold accumulation measured by neutron activationanalysis.

In addition to the observations through the first day after lasertreatment, patient follow-up occurs on weeks 1 and 2, and monthlythereafter for the 6 months following treatment.

Introduction

In the United States, approximately 46,000 cases of head and neck cancerare diagnosed on an annual basis, resulting in approximately 11,000deaths annually. Unfortunately, despite multidisciplinary treatmentefforts including surgery, radiation therapy, and chemotherapy, all ofwhich are associated with substantial morbidity to patients, five yearsurvival rates have not improved significantly over the last severalyears.

Nanoshell therapy can be used to selectively destroy solid tumors usingnear infrared illumination from a laser. Particles deliveredsystemically to the tumor serve as an exogenous absorber of this laserillumination to generate a thermal response.

Nanoshells

The nanoshells (e.g., Auroshells) can comprise a silica coreapproximately 110 to 125 nm in diameter (total diameter of particleincluding the gold shell is 140 to 170 nm); a functionalizing moleculeto allow gold colloid to adhere to the silica, APTES(3-aminopropyltriethoxysilane); a thin layer of gold (10-20 nm thick)affixed to the functionalized surface of the silica core. The process ofaffixing the gold shell to the silica core includes the production ofsmall colloidal gold nanoparticles 2 to 6 nm in diameter and theattachment of these nanoparticles to the amine groups present in theAPTES. These colloidal nanoparticles act as nucleating sites for thereduction of gold salt (HAuC14) in the presence of formaldehyde, tocomplete the shell layer. The gold shell comprises approximately 95% ofthe particle mass. The attachment of a layer of 5,000 MW PEG-thiol tothe surface.

Dose and Administration

In order to increase the EPR effect and AuroLase efficacy, at one hourprior to administration, the body temperature of the patient should beelevated by blankets or heating pads. A heating pad should be applied tothe tumor area. If the tumor is in the oral cavity or proximate to themouth or esophagus, cold beverages should be avoided.

AuroShell particles are administered intravenously at a rate of 2 ml perminute for the first 15 minutes of the infusion, increasing the rate toup to 10 ml per minute for the remainder of the infusion. Blood samplesare taken at 0.5, 2, 4, 8, 24 and 48 hours for determination of bloodclearance of AuroShell particles.

During the first 6 hours after administration, vaso-constrictivemedications should be avoided to maximize efficacy. The first group offive (5) patients receives an intravenous infusion of 4.5 ml/Kg ofAuroShell particles concentrated to 100 Optical Density (approximately1.3×10{circumflex over ( )}12 particles/Kg or 20 mg particles/Kg). TheAuroShell dose is increased from 4.5 ml/Kg to 7.5 ml/Kg of AuroShellparticles concentrated to 100 Optical Density (or approximately2.1×10{circumflex over ( )}12 particles/Kg or 34 mg particles/Kg) forthe second and third group if no significant unanticipated adversedevice effects related to AuroShell dose are observed in the firstgroup.

Laser Application

Calibration and verification of proper operation of the AuroLase systemis carried out prior to initiating the laser procedure and aresummarized below. Based on MRI, CT or similar imaging technique, thetumor region is mapped to a grid by the surgeon to allow a systematiclaser exposure of areas up to 1.0 cm outside the estimated tumor margin.This technique is based on an estimated 1 cm³ tissue treatment volumeper laser application. At a point 12 to 36 hours after AuroShellinfusion the patient is prepared for therapy. The patient may be sedatedor anesthetized as determined by the physician. The laser and thecooling pump is plugged in and connected together with the interlockcable. The optical fiber is connected to the laser and threaded into thecatheter. A sterile saline bag (1 liter) is hung and connected to theLaser Fiber cooling tubing set. The Laser Fiber cooling tubing is routedthrough the peristaltic cooling pump and connected to the inlet port ofthe catheter. The drain tube is connected to the outlet port of thecatheter and to a fluid collection bag. The cooling pump is turned onand allowed to prime the cooling lines. The laser settings should beadjusted to deliver the desired average power. The power output of thefiber is checked by inserting the catheter into a sterile tube mountedin the integrating sphere optometer. The LASER POWER knob is adjusted toproduce an average output power of as specified. The interstitialcatheter is placed proximal (within about 1 cm) to the tumor to betreated using the 14 gauge introducing catheter to avoid tumor seeding.The laser is applied for the specified time, then the fiber repositioned(using a fresh introducer if changing grid coordinates) to illuminateadditional areas of the tumor as previously mapped and the laserre-applied. Immediately after the laser illumination of the patient'starget lesion, a biopsy that will provide at least 6 mg of tumor tissue(such as an 18 gauge Tru-Cut needle biopsy 1 cm in length or similartechnique) is performed to measure the gold accumulation by neutronactivation analysis. If more than one tumor is being treated in a singlepatient, biopsies need only be obtained for the odd-numbered lesions(1st, 3rd, 5th, etc.).

Endpoints

For each patient, up to five (5) index lesions are identified. Indexlesions are those that are accessible to direct examination (examinationby fiberoptic nasopharyngoscopy or laryngoscopy is permitted) and tobiopsy. Each index lesion should have at least one dimension withlongest diameter≥15 mm using conventional techniques or ≥10 mm withspiral CT scan, and also be able to provide at least 6 mg of tumortissue by biopsy (such as an 18 gauge Tru-Cut needle biopsy 1 cm inlength or similar technique) for assessment by neutron activationanalysis. Tumor measurements are assessed from physical measurements andimaging techniques as appropriate for the lesion(s), e.g. CT, MRI,X-rays. Baseline measurements should be performed as close to AuroLasetreatment as possible. All measurable lesions up to a maximum of fivelesions are identified as target lesions and recorded and measured atbaseline. Target lesions are selected on the basis of their size(lesions with the longest diameter) and their suitability for accuraterepeated measurements (either by imaging techniques or clinically). Asum of the longest diameter (LD) for all target lesions will becalculated and reported as the baseline sum LD. The baseline sum LD willbe used as reference by which to characterize the objective tumor.

All other lesions (or sites of disease) are identified as non-targetlesions and should also be recorded at baseline. Measurements of theselesions are not required, but the presence or absence of each should benoted throughout follow-up.

Results

The patients have an 60-80 percent reduction of tumor size 6 monthsafter therapy. In 15% of the patients, the cancer is completelyeradicated. In 40% of the patients, no side effects are noted and normalprostate function is maintained.

Example 4

The following study describes results achieved using nanoparticles(Auroshells) with an embodiment of a laser catheter assembly asdescribed elsewhere herein.

A completed Pilot Study of AuroLase Therapy (e.g., the use ofnanoparticles and irradiation with a laser catheter assembly asdescribed elsewhere herein) in 11 human subjects with head and neckcancer under a cleared FDA IDE revealed no safety-related issues ineither particle delivery or the laser procedure.

Similarly, a pilot study of AuroLase Therapy in 22 human subjects withbiopsy-diagnosed prostate cancer resulted in no Serious Adverse Eventsin either particle delivery or the laser procedure. In total, as of thecurrent study, 33 human subjects have undergone AuroShell® particleinfusion and 26 have additionally undergone the related laser therapywith no reported Serious Adverse Events.

Preclinical safety has been established for AuroShell® particles invitro and in vivo in animal testing. Proof of concept studies have beencarried out using particles systemically directed against inoculatedtumors in the brain, directly injected into canine prostate and in humanprostate tumors grown orthotopically in mice.

With the basics of animal and human safety established, the focus of thecurrent study was to determine the efficacy of treatment with nanoshellsand subablative infrared irradiation of those nanoshells using a lasercatheter as disclosed herein. The treatment was performed on patientssuffering from prostate disease in a 22 patient pilot study. All 22patients were infused with nanoshells at 3 different dosing levels.Fifteen of these patients subsequently had the laser procedure as well.In a different study a further 13 patients were infused with nanoshellsand subsequently underwent an ultrasound-guided focal laser ablation oftumor tissue.

While this study was conceived and organized as a safety trial, a numberof whole-mount prostate sections of varying quality were available forhistopathological analysis. From these analyses it was possible to drawadditional conclusions about treatment efficacy.

The prostate study was carried out under the auspices of the Mexicanhealth safety commission, COFEPRIS, as an open-label, multi-center,single-dose pilot study of AuroLase Therapy in the treatment of subjectswith primary resectable prostate cancer. Only subjects that werescheduled for a radical prostatectomy were enrolled. The trial wasdivided into two arms: 1) Group 1 whose patients were infused withAuroShell particles one (1) day prior to a scheduled radicalprostatectomy, and 2) Group 2 whose patients were given an infusion ofAuroShell Particles one (1) day prior to a laser treatment, and 5±1 daysprior to a scheduled radical prostatectomy. Patients were followed for 6months following particle infusion with regular checks of vital signs,hematology, blood chemistry, and urinalysis. In total, seven (7)subjects completed the study in Group 1 and fifteen (15) subjectscompleted the study in Group 2.

Prostate Results

Between January 2011 and July 2012 we enrolled 22 prostate cancerpatients in Mexico. Each of these patients was infused with clinicalAuroShell particles (nanoshells as disclosed elsewhere herein), and 15of these underwent AuroLase Therapy laser treatment. Apart from thesafety results, two general conclusions were made based on theresults: 1) over a narrow range of power settings, laser energy goesfrom producing no observable thermal damage to producing thermal lesionsup to 1 cm across, and 2) Nuclear Activation Analysis (NAA) indicatesthere is enhanced AuroShell particle accumulation in prostaticadenocarcinoma as opposed to normal prostatic tissue.

Adverse Events

Only two Adverse Events were attributed to the infusion element ofAuroLase Therapy: a patient who suffered an apparent allergic reactionat the time of infusion, which resolved with intravenous medication, anda patient who suffered a single episode of a burning sensation of theepigastrium, for which no treatment was given, and which resolvedspontaneously. No Adverse Events were attributed to the laser treatment.

Infusion and Laser Dose

All patients were infused with the same 7.5 mL/kg (100 OD) dose ofparticles. This scales the particle dose by weight, and hence by bloodvolume. Fifteen (15) subjects in Group 2 received a laser treatment onthe day following infusion. A trans-rectal ultrasound probe was used todirect a single placement of the optical fiber system within the cortexof each hemisphere of the prostate. Adjustment of the position of theoptical fiber catheter within each hemisphere was based on the locationof the highest Gleason score indicated by the needle biopsy. The goal ofthe laser treatment was to demonstrate the safety of the procedure bydeveloping a laser dose that was ablative of tumor tissue, but not ofhealthy gland. Though this was a safety study, insights into efficacy byvarying the laser dose beginning at 3.0 W-3.5 W delivered for 3 min ateach site based on the optimal laser dose was established. In total, 6patients were treated at 3.5 W or below. Over the course of the fifteenlaser-treated patients this dose was increased incrementally to 5.0 W (3patients) delivered for 3 min, and then reduced to 4.5 W delivered foreither 3 or 4 min at each treatment site (6 patients).

Limitations of the Mexico Study and Interpretation of Results

Although quite satisfactory as an evaluation of safety, the Mexicoprostate study was limited in its ability to determine treatmentefficacy in the following ways:

1) The standard 12-punch biopsy used to diagnose and stage patients forthe trial did not provide accurate mapping of the number, extent, orspecific location of patient tumor(s),

2) The small, portable ultrasound system available, while sensitiveenough to insert the laser catheter into the general area of aparticular prostate hemisphere, did not provide the millimeter scaleresolution for reliably placing the laser catheter within or adjacent toa tumor, which was in any event invisible to the ultrasound system,

3) The logistics of fixing, cutting, embedding, transporting, assessing,and reporting on a given case rarely provided information timely enoughto adjust treatment parameters prior to a subsequent case, and

4) The private clinic where the research was performed was able toprovide whole mount slides for discrete, but incomplete sections of thelaser-treated prostates.

FIGS. 14A-14I show representative whole-mount sections from the last 9of the 15 laser-treated patients (those treated at >3.5 W; scale bars=1cm). These H&E sections (Hematoxylin and Eosin) show the spatialrelationship between the tumor tissue present 1001 and the optical fiberplacement 1002 in the prostate 1000, and any resulting zones ofcoagulo-necrosis 1003. For patients 208 and 210-215 at least one laserfiber placement was within or adjacent to regions of tumor. It isgenerally the case that treatments at the 4.5 W level producedcoagulo-necrosis conformal to tumor boundaries, but generally not innormal gland, while treatments at the 5.0 W level tended to producethermal lesions generally. It is further noted that in no case was theprostate capsule breached by the coagulo-necrotic zones.

FIG. 14A shows 4.4 W irradiation for 3 min and no damage in normalgland. FIG. 14B shows 4.4 W irradiation for 3 min with no damage innormal gland. FIG. 14C shows 5.0 W irradiation for 3 min withnon-specific damage in normal gland. FIG. 14D shows 5.0 W irradiationfor 3 min with no damage to normal gland and non-specific damage atperiphery of carcinoma. FIG. 14E shows 4.5 W irradiation for 4 min and adamage zone conformal to tumor boundary (1003) with no damage at asecondary site (1002). FIG. 14F shows 4.5 W irradiation for 4 min withno damage in normal gland and no damage at periphery of carcinoma. FIG.14G shows 4.5 W irradiation for 3 min with a thermal lesion thatoverlaps carcinoma and normal tissue, a thermal lesion in the normalgland enhanced by hemorrhage (upper left region, 1003). FIG. 14H shows4.5 W irradiation for 3 min with thermal damage in normal hemorrhagicgland. FIG. 14I shows 5 W irradiation for 3 minutes with thermal damagein the normal hemorrhagic gland (arrow to region, 1003).

FIG. 15 shows the relative accumulation of AuroShell particles inrepresentative samples taken from patients 210 and 211 (see FIGS. 14Dand 14E) as determined by NAA. Although the selected samples varyconsiderably as does the tumor grade as determined from the Gleasonscore, there is clearly a distinctly greater accumulation of particlesin tumor tissue.

Concept for Demonstrating Treatment Efficacy

The optical properties of tissues limit the depth of propagation ofoptical energy, thereby enabling a truly focal therapy. Heat evolvedfrom an energy source is inherently diffuse and nonspecific. Althoughthermally ablative heat can be made to propagate on the millimeterscale, it is not specific to tumor conformation. AuroShell particlesoffer the opportunity for more precisely localized conformal therapy andresult in tumor specific damage on the millimeter scale. The MRI fusionimaging approach, using ultrasound guidance based on a priori MRI fusionimaging, should permit the precise placement of the optical fibercatheter within or adjacent to the index prostate lesion targeted forablation.

Details for Demonstrating Treatment Efficacy

Particle-directed treatment can be made very focal. Over a narrow rangeof laser power settings, 4.0-5.0 W/cm, photothermal treatments can bemade to spare normal glandular tissue and thermally ablateparticle-containing adenocarcinoma and BPH.

As a result of the enhanced optical absorption resulting from thepresence of particles, AuroLase Therapy is able to generate photothermallesions by elevating target tissues to 55-65° C. over the course of a3-4 minute treatment time. These temperature profiles generatecoagulo-necrotic regions, which re-granulate and dissolve over thecourse of days, as opposed to thermally fixed lesions that tend not toresolve, while additionally appearing live on most histopathologicalexaminations. Results of photothermal ablation are fully realized within48-72 hours post treatment and are observable under MRI.

Since the accumulation of particles is a function of neovasculature andnot cell surface biomarkers of vessel and cell walls, AuroLase Therapycan be performed soon after (or prior to) chemotherapy and radiationtherapy. There is, as yet, no evidence that AuroLase Therapy efficacy isaffected by previous therapies.

Summary

Questions of safety have been answered both in terms of particle safetyand laser delivery.

A merging of MRI fusion imaging and the subsequent directed placement ofthe laser catheter represents a means of establishing the efficacy andutility of AuroLase Therapy for the treatment of localized prostatedisease, and represents the logical next step in the utilization ofAuroLase Therapy. The MRI-Ultrasound fusion approach is useful forresolving limitations identified in previous studies of AuroLase Therapygiven the ability to do: 1) pre-treatment target planning, and 2) guidedimagery for the accurate placement of the laser catheter in proximity tothe index lesion to be ablated.

Three-dimensional localization of the optical fiber catheter within theprostate, coupled with near real-time thermal data (ideally MRTI) wouldpermit the appropriate treatment power to be confirmed and the treatmenttime to be either lengthened or shortened in order to produce focalablation that conforms to the index lesion to be treated.

Testing in squamous cell carcinomas of the head and neck, caninemelanomas and carcinomas of the oral cavity, and in canine and humanprostate all demonstrate the focal nature of particle-directedphotothermal energy. Incorporation of an imaging modality can enableprecise lesion treatment. Further, the ability of particles to co-locateto neoplastic tissue can further enable lesion ablation conformal to thetarget tumors.

The potential benefits of AuroLase Therapy comprise a highly selectiveand rapid tumor destruction with minimal damage to surrounding tissueenabling a potentially curative treatment of tumors with minimumtoxicity. Preclinical studies have demonstrated that AuroLase therapy iseffective and causes no detectable systemic toxicity.

In summary, various embodiments and examples of methods, systems, anddevices for treating tumors have been disclosed. Although the methods,systems, and devices have been disclosed in the context of thoseembodiments and examples, it will be understood by those skilled in theart that this disclosure extends beyond the specifically disclosedembodiments to other alternative embodiments and/or other uses of theembodiments, as well as to certain modifications and equivalentsthereof. For example, some embodiments of the method are configured tobe also used with other types of devices and systems. This disclosurealso expressly contemplates that various features and aspects of thedisclosed embodiments can be combined with, or substituted for, oneanother. Accordingly, the scope of this disclosure should not be limitedby the particular disclosed embodiments described above, but should bedetermined only by a fair reading of the claims that follow or that maybe presented in the future.

What is claimed is:
 1. A laser illuminating system, comprising: a laserilluminator assembly comprising an elongate introducer probe with adomed, transmissive sealed end; an optical fiber with a diffuser tip andan optical fiber connector, the optical fiber connector being configuredto engage the laser illuminator assembly, wherein when the optical fiberconnector is engaged with the laser illuminator assembly, the diffusertip of the optical fiber is positioned within the laser illuminatorassembly; and a laser source configured to be in optical communicationwith the optical fiber and configured to transmit radiation through theoptical fiber to the laser illuminator assembly when the optical fiberconnector is engaged with the laser illuminator assembly; wherein, whenactivated, the laser source transmits electromagnetic radiation throughthe optical fiber and through the domed, transmissive sealed end of thelaser illuminator assembly.
 2. The system of claim 1, further comprisingan actuator configured to activate and deactivate the laser source. 3.The system of claim 2, wherein the actuator is a foot pedal.
 4. Thesystem of claim 2, further comprising: a coolant reservoir configured tobe in fluidic communication with the laser illuminator assembly; acoolant inlet tube configured to convey coolant from the coolantreservoir to the laser illuminator assembly; a pump configured to conveycoolant from the coolant reservoir to the laser illuminator assembly viathe coolant inlet tube to cool the optical fiber; and a coolant outlettube configured to convey coolant from the laser illuminator assembly.5. The system of claim 4, wherein the actuator is further configured tocontrol the pump.
 6. The system of claim 5, wherein the laser and thepump are configured to be activated by the actuator substantiallysimultaneously and wherein the laser and the pump are configured to bedeactivated by the actuator substantially simultaneously.
 7. The systemof claim 1, wherein the laser source is configured to deliver aradiation that is near infrared radiation.
 8. The system of claim 7,wherein the laser source is configured to deliver a radiation that has awavelength ranging from about 805 nm to about 810 nm.
 9. The system ofclaim 1, wherein the optical fiber comprises a diffusive portionconfigured to distribute radiation from the optical fiber and out of thelaser illuminator assembly.
 10. The system of claim 9, wherein a lengthof the diffusive portion of the optical fiber ranges from about 1.0 cmto about 1.8 cm.
 11. A laser illuminating system, comprising: a laserilluminator assembly comprising an elongate introducer probe with adomed, transmissive sealed end; an optical fiber with a diffuser tip andan optical fiber connector, the optical fiber connector being configuredto engage the laser illuminator assembly, wherein when the optical fiberconnector is engaged with the laser illuminator assembly, the diffusertip of the optical fiber is positioned within the laser illuminatorassembly; a laser source configured to be in optical communication withthe optical fiber and configured to transmit radiation through theoptical fiber to the laser illuminator assembly, wherein, whenactivated, the laser source transmits electromagnetic radiation throughthe optical fiber and through the domed, transmissive sealed end; acoolant reservoir configured to be in fluidic communication with thelaser illuminator assembly; a coolant inlet tube configured to conveycoolant from the coolant reservoir to the laser illuminator assembly; apump configured to convey coolant from the coolant reservoir to thelaser illuminator assembly via the coolant inlet tube to cool theoptical fiber; a coolant recovery bag in fluidic communication with thelaser illuminator assembly and configured to receive coolant from thelaser illuminator; and a coolant outlet tube configured to conveycoolant from the laser illuminator assembly to the coolant recovery bag.12. A laser catheter device comprising: an introducer probe comprising afirst lumen terminating in a sealed domed end configured to allow laserlight transmission; and an internal tube located within the first lumenof the introducer probe, the internal tube comprising a second lumen;wherein the introducer probe is configured to receive an optical fiber;wherein, when received, the optical fiber is positioned within thesecond lumen and is configured to transmit laser radiation through thedomed end of the introducer probe; and wherein the first lumen is influidic communication with the second lumen.
 13. The device of claim 12,further comprising a coolant inlet in fluidic communication with thesecond lumen and a coolant outlet in fluidic communication with thefirst lumen, wherein the laser illuminator assembly is configured toallow the passage of a coolant from the coolant inlet through the secondlumen into the first lumen and out of the coolant outlet.
 14. The deviceof claim 13, wherein the fluid inlet and the fluid outlet are configuredto interact with different connectors to prevent improper routing ofcoolant through the laser illuminator device.
 15. The device of claim14, wherein the fluid inlet and the fluid outlet are of different sexes.16. The device of claim 14, wherein the fluid inlet comprises a maleconnector and the fluid outlet comprises a female connector.
 17. Thedevice of claim 12, wherein the laser illuminator comprises the opticalfiber and the optical fiber comprises a diffusive portion configured todistribute radiation from the optical fiber and out of the laserilluminator assembly.
 18. The device of claim 17, wherein a length ofthe diffusive portion of the optical fiber ranges from about 1.0 cm toabout 1.8 cm.
 19. The device of claim 12, wherein an outside of theprobe is graduated.
 20. The device of claim 19, wherein the graduationsare about 4 mm apart.